U.S. patent application number 17/013180 was filed with the patent office on 2021-04-01 for electronic medication compliance monitoring system and associated methods.
This patent application is currently assigned to etectRx, Inc.. The applicant listed for this patent is etectRx, Inc.. Invention is credited to Neil R. Euliano, Glen Flores, Venkata V. Meka, Brent A. Myers, Jose C. Principe.
Application Number | 20210093248 17/013180 |
Document ID | / |
Family ID | 1000005273732 |
Filed Date | 2021-04-01 |
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United States Patent
Application |
20210093248 |
Kind Code |
A1 |
Euliano; Neil R. ; et
al. |
April 1, 2021 |
ELECTRONIC MEDICATION COMPLIANCE MONITORING SYSTEM AND ASSOCIATED
METHODS
Abstract
A system and method for monitoring a patient's compliance with a
medication regimen includes an electronic tag integral with or
attached to a medicine delivery device such as a capsule, the tag
haying an antenna and a receiver/transmitter, the system also
including a reader positioned externally for detecting the presence
and location of the delivery device in the patient.
Inventors: |
Euliano; Neil R.;
(Gainesville, FL) ; Myers; Brent A.; (Palm Bay,
FL) ; Principe; Jose C.; (Gainesville, FL) ;
Meka; Venkata V.; (Oakland, CA) ; Flores; Glen;
(Gainesville, FL) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
etectRx, Inc. |
Gainesville |
FL |
US |
|
|
Assignee: |
etectRx, Inc.
Gainesville
FL
|
Family ID: |
1000005273732 |
Appl. No.: |
17/013180 |
Filed: |
September 4, 2020 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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16408642 |
May 10, 2019 |
10765360 |
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17013180 |
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15687212 |
Aug 25, 2017 |
10292642 |
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16408642 |
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14726899 |
Jun 1, 2015 |
9743880 |
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15687212 |
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12881572 |
Sep 14, 2010 |
9047746 |
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14726899 |
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11458815 |
Jul 20, 2006 |
7796043 |
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12881572 |
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60734483 |
Nov 8, 2005 |
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60700963 |
Jul 20, 2005 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 5/06 20130101; A61B
5/4205 20130101; A61B 5/14539 20130101; G16H 20/13 20180101; G08B
21/04 20130101; G08B 23/00 20130101; A61B 5/4833 20130101; A61B
5/073 20130101; A61B 5/065 20130101; A61B 5/07 20130101; A61B 5/42
20130101; G16H 20/10 20180101; G08B 21/0407 20130101; A61B
2560/0209 20130101; A61M 2205/3592 20130101; A61B 5/285 20210101;
A61B 2560/0214 20130101 |
International
Class: |
A61B 5/00 20060101
A61B005/00; A61B 5/07 20060101 A61B005/07; A61B 5/145 20060101
A61B005/145; G08B 23/00 20060101 G08B023/00; G16H 20/10 20060101
G16H020/10; A61B 5/06 20060101 A61B005/06; G08B 21/04 20060101
G08B021/04 |
Claims
1. An electronic system for monitoring a patient's compliance with
a medication program, the system comprising: an ingestible medicine
delivery device; a tag fitted with the delivery device, a tag
electronic circuit carried by the tag, the circuit having means for
processing and transmitting one or more out-link radio frequency
signals to indicate the presence of the delivery devices with in
the patient's body; an electronic reader adapted to be positioned
externally adjacent the patient, wherein the reader having means
for processing the one or more out-link radio frequency signals
received from the tag; and a remote device configured to receive
information from the electronic reader and generate data indicative
of the patient's mediation compliance with the medication program
based on the information received from the electronic reader.
2. The electronic medication monitoring system recited in claim 1
wherein the remote device is further configured to transmit the
generated data to a health provider of the patient.
3. The electronic medication monitoring system recited in claim 1,
wherein the generated data comprises a real-time estimation of
blood levels associated with a specific medication based on one or
more pharmacodynamics models and pharmacokinetics models.
4. The electronic medication monitoring system recited in claim 1,
wherein the generated data comprises a medication refill
request.
5. The electronic medication monitoring system recited in claim 1,
wherein the generated data comprises an instruction on adverse drug
reaction.
6. The electronic medication monitoring system recited in claim 1,
the generated data comprises a notification for the patient based
on mediation compliance status of the patient.
7. The electronic medication monitoring system recited in claim 1,
wherein the circuit further comprises means for receiving one or
more in-link radio frequency signals.
8. The electronic medication monitoring system recited in claim 1,
wherein the delivery device comprises a capsule having an outer
surface and an inner surface with the tag fitted to one of the
inner and outer surfaces.
9. The electronic medication monitoring system recited in claim 1,
wherein the one or more out-link radio frequency signals are coded
with data representing at least one of the patient's
identification, an identification for a medication trial, a
medication type, and elapsed time of the tag in the patient's
gastrointestinal tract.
10. The electronic medication monitoring system recited in claim 1,
wherein the reader further comprises means for receiving and
processing out-link radio frequency signals from multiple tags
simultaneously within the patient's body.
11. An ingestible electronic tag system for use in tracking
ingested medication in a patient's body, the tag system comprising:
an electrically insulated substrate having an upper surface and an
opposing lower surface; a tag electronic circuit fitted to one of
the surfaces of the substrate, the tag circuit having means for
transmitting one or more out-link signals containing data
representative of the status of the tag and its location; and
antenna means disposed across one of the substrate surfaces and
electrically coupled to the tag electronic circuit for transmitting
the one or more out-link signals.
12. The ingestible electronic tag system recited in claim 11,
wherein the substrate comprises an ingestible coated paper, and
wherein the coating and the paper dissolve in a presence of
predetermined gastric fluids.
13. The ingestible electronic tag system recited in claim 11,
further comprising a galvanic gastric sensor fitted with the tag
and coupled with the tag electronic circuit, the sensor providing
varying inputs to the tag electronic circuit dependent upon
location of the sensor in the patient's body.
14. The ingestible electronic tag system recited in claim 11,
further comprising an electronic reader adapted to be positioned
adjacent the patient's body, the reader having means for receiving
and processing the one or more out-link signals from the tag
electronic circuit.
15. The ingestible electronic tag system recited in claim 14,
further comprising a remote device configured to receive
information from the electronic reader and generate data indicative
of medication compliance status of the patient based on the
information received from the electronic reader.
16. The ingestible electronic tag system recited in claim 15,
wherein remote device is further configured to transmit the
generated data to a health provider of the patient.
17. The ingestible electronic tag system recited in claim 15,
wherein the generated data comprises a real-time estimation of
blood levels associated with a specific medication based on one or
more pharmacodynamics models and pharmacokinetics models.
18. The ingestible electronic tag system recited in claim 15,
wherein the generated data comprises a medication refill
request.
19. The ingestible electronic tag system recited in claim 15,
wherein the generated data comprises an instruction on adverse drug
reaction.
20. The ingestible electronic tag system recited in claim 15,
wherein the venerated data. comprises a notification for the
patient based on medication compliance status of the patient.
Description
CROSS RFFERFNCE TO RFLATED APPLICATIONS
[0001] This application is a continuation of U.S. application Ser.
No. 15/687,212, filed Aug. 25, 2017, which is a continuation of
U.S. application Ser. No. 14/726,899 filed Jun. 1, 2015, now U.S.
Pat. No. 9,743,880, issued on Aug. 29, 2017, which is a
continuation of U.S. application Ser. No. 12/881,572 filed Sep. 14,
2010, now U.S. Pat. No. 9,047,746 issued on Jun. 2, 2015, which is
a continuation-in-part of application Ser. No. 11/458,815 filed
Jul. 20, 2006, now U.S. Pat. No. 7,796,043 issued on Sep. 14, 2010,
which claims priority to U.S. Provisional Application Ser. Nos.
60/700,963, 60/734,483 and 60/746,935, filed Jul. 20, 2005, Nov. 8,
2005 and May 10, 2006, respectively, the entire contents of which
applications are herein incorporated by reference in their
entirety.
FIELD OF THE INVENTION
[0002] The present invention relates to electronic systems and
methods for monitoring medication compliance.
BACKGROUND OF THE INVENTION
[0003] Non-compliance of patients to drug regimens prescribed by
physicians can cause a multiplicity of problems, including negative
patient outcomes, higher healthcare costs and an increased risk of
the spread of communicable diseases. Compliance monitoring is also
critical in, for example, pharmaceutical clinical trials,
geriatrics and mental health/addiction medicine. Poor medication
compliance has a significant negative impact on patients,
pharmaceutical manufacturers and the healthcare system in general.
Non-compliant patients suffer from increased mortality, increased
recurrence of chronic conditions and increased hospital and nursing
home admissions. By some estimates, as much as 25% of all
healthcare costs could be avoided if patients reliably took their
prescribed medications.
[0004] Annual drug development spending has increased more than
twelve times in inflation-adjusted dollars over the past three
decades. Clinical trials consume a major portion of the development
time and costs of introducing a new drug into the market. Knowing
with certainty a patient's adherence significantly improves the
understanding of the results from a clinical trial in terms of
safety, efficacy, dose response relationship, pharmacodynamics,
side effects and other results. For instance, in a beta-blocker
heart attack trial the death rate was reported at 13.6% in subjects
whose compliance was less than 75% compared to 5.6% in subjects
whose compliance was over 75%. None of the existing methods of
measuring adherence offer both a qualitative and a quantitative
measure with proof-positive detection of ingestion of the
medication. Accordingly, measuring medication regimen compliance
continues to be a major problem. The only statistical recourse is
to enroll large numbers of patients, which dramatically increases
the cost of clinical drug trials that in turn increases the cost of
the final marketed medication.
[0005] Compliance monitoring also provides significant benefits in
market areas where patient adherence to a drug therapy protocol is
vital to preventing or avoiding high-cost consequences for the
patient or community. Strict regimen adherence is important for
preventing emergence of drug-resistant strains of infectious
diseases that can occur when proper dosing schedules are not
followed. Such resistant strains result in increased transmission,
morbidity and mortality and are more expensive to treat or cure,
often by one or two orders of magnitude.
[0006] A traditional method of increasing compliance is direct
observance, but this is obviously difficult to administer and
impractical on a large scale. Other techniques include blood
sampling, urine sampling, biological marker detection,
self-reporting, pill counting, electronic monitoring and
prescription record review. These techniques are either invasive or
prone to tampering.
[0007] In vivo biotelemetry and monitoring have been used for
monitoring embedded oxygen, sensing glucose levels, fetal
monitoring and hormone measuring. Passive radio-frequency
identification (RF ID) techniques have been suggested to provide
biotelemetry by including external sensors into existing commercial
systems. However, RFID was not designed to operate in vivo, and the
transmission of electromagnetic signals from embedded or internal
sensors is hampered by attenuation and reflections from the
body.
[0008] Therefore, it would be beneficial to provide an active
electronic device, system and method for non-invasively monitoring
drug compliance in a facile manner.
SUMMARY OF THE INVENTION
[0009] The present invention is directed to an electronic drug
compliance monitoring system and associated methods that utilizes a
pill having an active electronic transmission capability and
external means for receiving that transmission to sense the
presence of the pill in the patient's internal organs.
[0010] It is believed that the present invention has several
advantages over currently known methodologies. For example, the
monitor documents that the prescribed medication was actually
present in the digestive system, whereas not even directly observed
therapy can conclusively determine that the patient swallowed the
pill. The system can be used with medication dispensers, timers,
reminders, external communications, and database systems to create
a complete medication compliance monitoring system. The system
provides factual evidence of patient's compliance to the regimen,
medication, knowledge that is critical, for example, to assessing
the outcome of a clinical trial including the systematic removal of
non-compliant subject data. Trials that pay subjects to participate
in clinical studies can corroborate compliance. Further, the system
permits remote patient monitoring whereby the monitor can be
integrated into a wireless system communicating directly with a
central database, reducing costs by minimizing required patient
monitoring/interaction. Finally, the system is noninvasive and does
not require the collection of a bodily fluid.
[0011] The features that characterize the invention, both as to
organization and method of operation, together with further objects
and advantages, will be better understood from the following
description used in conjunction with the accompanying drawing. It
is to be expressly understood that the description and drawing are
for the purpose of illustration and is not intended as a definition
of the limits of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
[0012] FIG. 1 is a schematic diagram of the medication compliance
system of the present invention.
[0013] FIG. 2A is one embodiment of a capsule having a planar
substrate with an antenna and electronics wrapped about a portion
of the capsule.
[0014] FIG. 2B illustrates a capsule having a multiple-coil antenna
wrapped about its periphery.
[0015] FIG. 2C illustrates a capsule having a single-coil antenna
wrapped about a portion of its periphery.
[0016] FIG. 3 is a schematic chart that illustrates the use of an
electronic capsule with a wristband reader that is in communication
with a cell phone, and which in turn can be used to forward
information to a data collection center.
[0017] FIG. 4 is a schematic diagram illustrating the onboard
electronics fitted with an electronic pill or capsule like that
shown in FIGS. 1, 2A-2D and 3.
[0018] FIGS. 5A and 5B illustrate techniques used to mate an
electronic tag shown in FIGS. 1 and 3 with the inside surface of a
capsule (FIG. 5A) or the outer surface (FIG. 5B).
[0019] FIGS. 6A, 6B and 6C are schematic side views illustrating
the layers used to fabricate an electronic tag in accordance with
different embodiments of this invention.
[0020] FIG. 7 is a circuit diagram for an exemplary activation
switch circuit using a conductive sensor with a NMOSFET
transistor.
[0021] FIG. 8 is a circuit diagram for an exemplary deactivation
switch circuit using a MOSFET transistor.
[0022] FIG. 9 is a circuit diagram for an exemplary MOSFET
sensor-based bio-switch.
[0023] FIG. 10A is a top perspective view of an ingestible switch
in accordance with the present invention utilizing a hydrogel
circuit breaker.
[0024] FIG. 10B depicts the switch of FIG. 10A, with a swollen
hydrogel circuit breaker after exposure to gastrointestinal
fluids.
[0025] FIG. 11 is a schematic side view of a galvanic gastric
sensor for utilization with the electronic tag shown in FIGS. 1 and
3.
[0026] FIG. 12A is a summary of the results of testing of several
phosphate electrodes at different modes.
[0027] FIGS. 12B and 12C are coded charts depicting the results set
forth in FIG. 12A for a 20K Ohm load and a 1K Ohm,
respectively.
[0028] FIG. 13 is a block diagram illustrating the electronics
associated with the tag integrated circuit.
[0029] FIG. 14 is a block diagram illustrating the overall inlink
and outlink communications between the electronic tag taken
internally by a patient, and the external reader utilized to
communicate with the tag.
[0030] FIG. 15 is a timing chart illustrating the periodic
transmissions from the reader to the tag and the data bursts from
the tag to the reader.
[0031] FIG. 16 is a chart depicting the content of the inlink
transmission from the reader to the tag.
[0032] FIG. 17 is a chart depicting the content of information
contained it the data bursts from the tag to the reader.
[0033] FIG. 18 depicts a timing chart for uplink transmissions from
multiple tags to the reader.
[0034] FIG. 19 is a further block diagram of the overall system,
illustrating a specific example of conductive transmissions from
the reader to the tag at 4 MHz and radiative outlink transmissions
from the tag to the reader at 400 MHz by way of example.
[0035] FIG. 20 is another timing diagram illustrating the operation
of the system of the present invention.
[0036] FIGS. 21A and 21B are block diagrams illustrating further
aspects of the operation of the system.
[0037] FIG. 22 is a side view illustrating an alternate
construction for the electronic capsule to permit a portion of the
electronics to be carried within the capsule.
[0038] FIG. 23 is an exploded illustration depicting, from left to
right, the attachment of an integrated circuit chip to the tag
connected to the low frequency and high frequency antenna areas,
and the wrapping of the tag about a capsule (right hand side).
[0039] FIGS. 24A and 24B depict exemplary constructions of a
capsule with a tag in accordance with this invention.
[0040] FIG. 25 is a top view of the tag, illustrating various
dimensions and small component details and a wrapped
configuration.
[0041] FIG. 26 is a cross-sectional side view of the tag,
illustrating various dimensions associated with the elements
depicted in schematic form in FIGS. 6A and 6B.
[0042] FIG. 27 sets forth representative dimensions of the capsule
and tag.
[0043] FIG. 28 is a top view of a wrist band reader feature shown
in FIG 3.
[0044] FIG. 29 depicts a patch reader wearable by a patient.
[0045] FIG. 30 depicts a pill container having an on-board
reader.
[0046] FIG. 31 is a block diagram of the reader 19 in FIG. 1.
DETAILED DESCRIPTION OF THE PRFFERRFD EMBODIMENTS
[0047] A description of the preferred embodiments of the present
invention will now he presented with reference to FIGS. 1-30.
[0048] Noting FIG. 1, a system 10 for monitoring medication
compliance in a patient 16 comprises an electronic sensor,
preferably in the form of a small monitor or reader 11 that
includes an RF transceiver 12 and one or more antennas 13. The
antenna 13 can be external or internal to the monitor 11 and can be
implemented in a variety of ways as known in the art, including an
on-chip antenna or simple pads or electrical contacts that function
as an antenna. The reader 11 detects the presence of an electronic
pill 14 in, for example, the gastrointestinal tract of the patient
16. As shown the electronic pill 14 has a tag 15 attached to or
part of the pill 14. For purposes of this disclosure, the term
"pill" can include a capsule or other form of medication
administration or testing. The system 10 is designed to detect the
pill 14 when located in the patient's mouth M, esophagus E, stomach
S, duodenum D, intestines I or rectum R.
[0049] With continued reference to FIG. 1, the system 10 includes a
tag 15 fixed with the pill 14, either internally or along the outer
surface, or both. After ingestion of the pill 14, the tag 15 is
made electronically active and begins communication with the
external reader 11. The external reader 11 in one embodiment is in
a housing 19 worn by or attached with the patient 16 so as to he
comfortable and easy to wear continuously to ensure it is always
with the patient.
[0050] The electronic pill 14 comprises an orally ingestible and
biocompatible drug-transporting device with embedded or attached
electronic circuits that communicates with the external wireless
reader 11. As described in greater detail below, the electronic
pill 14 uses, for example, a silicon-based integrated circuit
and/or other passive components such as coil antennae and
capacitors. The circuit can incorporate millions of transistors,
patterned through various semiconductor processing steps, to
provide an enormous amount of intelligence. For instance, the
electronic pill 14 can store a patient's medical history in
addition to detailed information about a drug being administered,
provide a unique identification number, and implement advanced
communication circuits and protocols to reliably transmit data to
an external wireless reader 11.
[0051] Turning now to FIG. 2A, the electronic pill 14 preferably
comprises a drug-transporting device, such as a capsule 17 that has
associated therewith the electronic tag 15. Noting FIG. 1, a signal
18 received by the reader 11 from the electronic circuit 30 after
ingestion of the capsule 17 is thus indicative of medication
compliance. The term "drug-transporting device" is not intended as
a limitation, and other compositions and devices for delivering
medication are intended to be subsumed hereinto as known in the
art. Alternatively, the capsule 17 may be devoid of medication to
serve as a placebo during a drug trial.
[0052] Referring again to FIG. 2, the electronic components of the
electronic pill 14 are capable of wireless transmission and
reception over short distances (i.e., in the range of 20-30 cm).
The electronic components in the circuit 20 (i.e., antenna 21,
power source 22, and silicon chip 23), once hermetically sealed and
packaged, is small enough to fit inside or on the outside wall of
the capsule 17. This level of miniaturization is feasible owing to
integration and circuit scaling trends associated with standard
CMOS technologies.
[0053] With continued reference to FIG. 2A, a small chip or other
electronics 47 is attached to the substrate 45 as well. This chip
47 provides a great deal of functionality including but not limited
to two way communication and complex protocols, energy harvesting
(mechanical, electrical, etc), sensing of conditions such as
location of the tag via pH, chlorine content, etc., encryption, and
identification code storage and transmission.
[0054] Referring now to FIG. 3, the complete system is principally
composed of a Data Reader 111 and multiple tags 15 attached to
medication 14. Bidirectional data 50/52 is exchanged between the
reader 111 and the tag 15. The reader 111 probes the one or more
tags 15 inside the body 10 and coordinates the communication to
allow multiple ingested tags to communicate simultaneously,
sequentially, or in other ways to permit multiple communication
pathways. The tags 15 communicate their unique identification data
and whether they are in the GI tract. The reader 111 then provides
output data 58 to a user interface 54 such as a laptop or
smartphone enabling real-time upload 59 of medication events to a
remote database 60 or other location.
[0055] The data link from the reader to tag 50 is defined as the
"in-link" path. Preferentially, in-link data to the tag includes
synchronization, signaling, address, and tag configuration
information. Preferentially, the reader 111 transmits information
by way of differential metallic skin contacts. The signal passes
through the body and is sensed by the tag through a differential
probe network.
[0056] The data link from the tag to the reader 52 is defined as
the "out-link" path. Preferentially, the out-link data to the
reader includes gastrointestinal (GI) sensing, pharmaceutical,
adherence, signal level, and address information. Preferentially,
the out-link channel 52 is composed of a radio frequency signal
traveling through both the body 10 and the free space between the
body and reader antenna. A small antenna (RFF) on the tag 15
radiates the out-link signal 52 which is received at the reader
111. The reader 111 is capable of receiving signals 52 from
multiple tags 14 simultaneously.
[0057] All of these components work together to complete a system
that can accurately detect a medication event, including the time
of ingestion, the dosage, and specific identification of the
medication. This information is then used to verify critical
compliance with drug therapy. This data can also be used in
combination with other patient data to improve adherence and
treatment outcomes.
[0058] In the embodiment shown in FIG. 2B, the capsule 17 has an
antenna 40 printed or attached that can be detected externally. In
one such embodiment, an externally induced magnetic field with a
time-varying oscillatory component impinging upon a resonant tank
in the pill (i.e., formed by a transponder coil antenna and a
parallel capacitor located in the tag 15) causes the current
circulating in the tank to increase. The peak current at the
frequency of resonance can induce a small but detectable change in
the reader coil impedance. Since the coils are only loosely
coupled, the resonant peak detection experiment can characterize
the range over which this effect can be used to detect the presence
of a pill.
Marker/tag Detail and Manufacturing
[0059] The following sections describe the detailed construction of
the tag 15. Referring to FIG. 4, the tag 15 comprises a body
interface and antenna 203 that allows for the in-link 50 and
out-link 202 communication. The ingestion detection subsystem 208
utilizes the body interface and antenna system 203 to determine
when the medication actually resides in the body 10 and in
particular in the digestive tract M,E,S,D,I,R. A receive subsystem
204 implements the in-link 50 communication and interfaces between
the body interface and antenna subsystem 203 and a control
subsystem 209. A transmission subsystem 206 implements the out-link
52 communication and interface between the control subsystem 209
and the body interface and antenna subsystem 203. An energy
harvesting subsystem 205 captures energy from either the body
interface 203 or from the environment that the tag 15 resides in,
for example the motion or temperature of the device. The energy
harvesting subsystem 205 provides energy which is stored in an
energy storage system 207 and to the tag 15 in general to operate
the components and provide sufficient power for outlink 52
transmission. The control subsystem 209 coordinates and controls
the differing components of the tag 15 and implements any
communication protocol, sensor measurements, maintains tag memory
for various identification information, and implements any other
functionality required by the tag 15. The tag 15 can be attached to
the medicine in a variety of ways, either by being built into the
medication, build onto the medication, being printed onto the
medication, or by being attached onto the outside or inside of the
medication carrier (i.e. a capsule). A preferred embodiment is to
build the tag 15 on a biocompatible substrate 45 that can be built
in high quantities and then later attached or built into a capsule
17, for example.
Substrate (Printing and Tag)
[0060] Referring now to FIGS. 5A and 5B, in another embodiment of
the tag 43 and the antenna 44 are printed on a flexible substrate
45 that is biodegradable and digestible, such as a flat sheet-like
material, and includes an electronic chip 47 mounted on the
substrate. This substrate 45 is then placed on or wrapped around
the capsule 46. The antenna 44 is preferably printed in a way that
when the material 45 is wrapped around a capsule 46, connections
can be made from one end of the sheet 45 to the other, thus forming
the antenna 44 as a continuous loop. Printing on both sides of the
material 45 simplifies this process by using a technique similar to
circuit board manufacturing with through-holes. Preferably, the
substrate should have sufficient rigidity for manufacturing and
attachment, be easily and safely digested, be flexible for wrapping
around a pill or capsule, and withstand temperatures required for
manufacturing and sterilization.
[0061] There are relatively few materials for substrates 45 and 74
that are both easily and safely digested and can also withstand
temperatures required for bonding the chips 47 and 71 to the
antennae 44 and 72 (up to 190.degree. C.) or the sintering of
metallic inks. In one embodiment, an enteric coating commonly used
in colonic-targeted drug release, is utilized to create a flat and
flexible substrate that meets these requirements and has been used
in prototype tags.
[0062] Enteric coatings are commercial materials with good
flexibility and proven biocompatibility. They are currently used in
aspirin, acetaminophen and other drugs that upset the stomach, as
they resist disintegration at low pH. Enteric coatings usually
begin to disintegrate at a pH above 5.5 or higher, which is the
typical pH of the duodenum and small intestine. Enteric coatings
include but are not limited to
polymethacrylate-polymethylmethacrylate (PMA-PMMA) copolymers and
cellulose acetate phthalate (CAP), which are commercial coatings
under names of "Eudragit" and "Aquacoat CPD" that are readily
available as pre-mixed solutions.
[0063] Referring now to FIG. 6A, in another embodiment, the
substrate 45 can be manufactured with a coated paper to create a
biocompatible coated paper substrate system 260 to provide more
advantageous properties. A paper substrate 82 coated with a coating
254 provides improved mechanical properties, increase printing
strength, reduced dissolution time, and allows tier alternative
printing methods, while maintaining biocompatibility. Enteric
coated paper provides a smooth texture 256 for the paper 82 and
allows for antenna patterns 266 to be easily transferred onto it.
The paper 82 also breaks up rapidly once the coating 254 dissolves.
Preferentially, the paper 82 is coated on all sides, but in some
implementations coating only the top of the paper is required. In
addition, a biocompatible adhesive 252 is applied to the bottom of
the paper when the tag 15 will be applied to the outside of the
medication. When adhesive 252 is included, a protective backing 258
is used to simplify handling and attachment to the medication.
[0064] The biocompatible coated paper system 260 of FIG. 6A
addresses manufacturing problems of electroplating/electroetching
on biodegradable substrates. Preferentially, biocompatible paper 82
is a mixture of biodegradable materials distributed in impregnated
and/or on coated the paper in a number of ways. Paper 82 can be any
substance that can be used as a flexible and strong biocompatible
substrate in the dry state but weakens in the wet state. Rice
papers, pulp papers, plant-based fiber papers including linen
papers are all substrates that can be used with a biocompatible
material coating or impregnation. The paper 82 itself is also
biocompatible. The biocompatible substances 254 used for coating or
impregnating the paper alter the dissolution properties, thermal
properties, mechanical properties, biodegradation rates and other
properties of the paper 82. The biodegradable materials included in
the construction of the biodegradable substrate 260 allow for
digestion of the substrates 45 and 74 and prevents untoward effects
such as lodging in the stomach of the substrate or pill itself, as
may occur with non-degradable and smoothly-surfaced polymeric
substrates.
[0065] The substrates 45 and 74 allow for the placement of a
metallic trace for antennae 266, chips 47 and 71, or other
electronics via electro-plate, bonding, gluing, adhesive or
printing. The antenna 266 may be covered in a protective coating
268 to prevent digestion, protect the antenna from handling, and
dielectrically isolate the antenna from the environment. The paper
82 is superficially coated with the biodegradable substance such as
polymethyl methacrylate-polymethacryalte, cellulose acetate
phthalate, poly lactic acid, poly glycolic acid, various sugars,
oils, waxes or proteins.
[0066] The biocompatible materials 254 added to the paper also
allow for increased stability of paper materials in more extreme
environments, including those of very high temperature and
humidity, preventing the tag 15 from warping or deforming (and
possibly fracturing the antenna 266). Referring to FIG. 6B, the
substrate 45 is coated in a multi-layer or patterned method with
multiple layers of coatings 254, 264 such that various portions of
the tag can be exposed or broken in the body 16 at varying times or
locations. At different times or locations in the body, different
coatings may dissolve exposing different types or portions of the
antenna 266 or sensors to the body 16. These varying conditions
provide information to the system allowing for determination of
ingestion time or tag 15 location. Referring to FIG. 6C, a
cross-sectional side view of an alternate form of the system 260A,
the coatings can be patterned such that different portions of the
paper 82 are coated with different coatings. This multi-layer or
multi-coated system 260A tracks the progress of the substrates as
they pass through the digestive tract M,E,S,D,I,R or encounter
different solutions in the body 16. In a preferred embodiment, each
coating 254, 264 is an Enteric coating that is formulated to
dissolve in specific areas of the human body 16. In combination
with a multi-level electronic sensor and in the form of an
electronic pill, the location of the medication is tracked through
the human body. As each layer of the substrate 254,264 dissolves in
its pH or chemically sensitive environment, a new electronic
sensor, which by way of example can be a galvanic cell is exposed.
In addition to exposing different sensors or probes in different
portions of the body 16, the selective dissolution of the coatings
in different parts of the body 16 alters the transmission
properties of the antenna 266 or system 260A in general, thus
making the location of the tag 15 in the body detectable without
separate sensors.
[0067] Various bodily chemicals and even organisms (and their
respective chemicals) can cause the degradation of the materials
used with the systems 260 and 260A. Enzymes, hormones, cells (blood
cells), proteins, acids, ions, bacteria, and so forth can
contribute to the degradation of the substrates or any of the
substrate layers.
[0068] Furthermore, in another embodiment, the system 10 is
triggered to dissolve in the patient's body 16 in the presence of
both a bodily chemical and an external impulse for additional
control. For example, the sensitivity of chemical breakdown is
enhanced by the application of RF energy to the substrates 260,
260A (producing heat or otherwise) from an outside RF source.
[0069] The system 10 may also be loaded with various degradation
control chemicals that can delay or hasten degradation rates. This
is useful if the processing of substrate layers that require
extra-thick amounts of a certain layer to be mechanically stable or
if a layer requires another chemical in addition to the ones found
in the human body 16 to begin degrading appreciably.
Antennas and Coatings
[0070] Pill or capsules 14 is typically printed with edible inks of
pharmaceutical grade to uniquely identify the product and provide
additional information such as company logo, brand name, and dosage
information. In accordance with this invention, these edible inks
are replaced with conductive and biocompatible silver inks to
pattern small antennas 266 (FIG. 6A), coils 41 (FIG. 2C) or
deposited conductive pattern 44 (FIGS. 5A, 5B) directly on the
capsule 14, 17. Other compositions known in the art are also
contemplated such as but not limited to carbon black, iron, gold,
copper, zinc, and conducting polymers.
[0071] Thus, by way of printing, etching, or electroplating,
miniature antennae 266 are made of silver, carbon black, copper, or
other biocompatible coatings. Silver, copper, zinc and other metals
are substantially biologically inert, and when ingested in small
amounts, are nontoxic to humans and pass through the body without
being absorbed into tissues. Furthermore, the conductivity of most
of these metals is very high, making them excellent conductors.
Therefore, the antenna 266 performance not only depends on physical
size constraints, but also on the total usable concentration of
conductive material.
[0072] Coatings, Referring again to FIGS. 6A and 6B, it is
preferred to encapsulate the components of the tag with a coating
268 for multiple reasons, including but not limited to: electrical
isolation from the conductive fluids of the GI-tract M,E,S,D,I,R,
prevention of dissolution or exposure to the body for safety, and
selective dissolution at different locations in the body 16. For
example, the coating 268 prevents contact with the body, limiting
exposure of the materials to the patient 16. Certain coatings can
be utilized that are pH or otherwise selectively dissolved in
different portions of the GI tract. In a preferred embodiment,
enteric coatings that do not dissolve until they reach the
intestine 1 or other locations, where very little digestion occurs.
This allows the material to break up before excretion but not leach
materials into the blood stream. It is also desirable to activate
the tagging system only after the patient has ingested the pill 14.
Once ingested, the pill 14 is exposed to stomach acids that eat
away coatings 268 on the surface of the capsule 17, 46. Coatings 52
(or 268) may be applied or selectively applied to cover parts of
the tag or capsule/pill. In one embodiment, these coatings 268 are
applied selectively to cover certain portions of the tag and
capsule but allow other portions of the tag and capsule to break
down. This allows the tag to change shape or break down in such a
way that it easily passes through the digestive tract while still
protecting sensitive materials from digestion.
[0073] In another embodiment, the conductive layers of the antenna
266 on the tag 15 are made by incorporating a metal that can
dissolve, such as iron filings under a temporary protective layer
268 such as polyglycolic acid or by incorporating particles that
are nontoxic by virtue of being non-absorbable (e.g., silver or
carbon). Degradation of the matrix releases particles that move
through the digestive system of the patient 16 without absorption.
Such particles are present above a percolation threshold for
conductive "contact" (within 1000 .ANG.), and reside in a
degradable matrix such as polylactic/glycolic acid or starch. The
degree of conductivity is adjusted by the degree of close contact
and by the number of contact points (volume fraction). Particles
that are not spherical can be added at lower levels to get good
conduction. Hence, graphic carbon plates can reach a percolation
threshold at lower levels, and silver can be used as planar
particles as well.
[0074] In a preferred embodiment, the integrated circuit 47 is
encapsulated or coated in a protective coating such that it is not
exposed to the body 16 and its digestive process. Packaging
preferably does not interfere with the RF communication but
provides enough safety for human studies. Methods of use allow
access to the aqueous environment for sensors while still ensuring
safety.
Energy Harvesting
[0075] Power sources for body-powered electronic pills must be
biocompatible, small in size with the appropriate form factor,
capable of delivering high power with good maximum discharge
current characteristics and low self-discharge, and provide long
calendar life. Referring to FIG. 4, many techniques exist for
harvesting power 205 and storing the power 207 within the circuit
47 for use with the tag 15. For example, a simple capacitor can be
used to store the energy at block 207 owing to the short duration
of the active nature of these devices (less than 1 minute). The
capacitor is embedded into the pill electronics and charged from
block 205 by a handheld device via a magnetic field or other
mechanism before being swallowed by the patient 16. The capacitor
holds this charge until activated by a triggering mechanism, such
as the dissolving of a specially coated switch by stomach acid.
[0076] In one embodiment of the energy harvesting block 205, the
chemical energy of the stomach contents is converted into
electrical energy. For instance, the chemical reaction between the
stomach acid and a zinc electrode oxidizes the zinc, creating an
electric current via a metal electrode making the return path. In
another embodiment, the system converts mechanical motion (e.g.,
peristaltic and other motion common in the digestive tract) into
electrical energy.
[0077] In one embodiment, the energy harvesting system 205 harvests
the energy of the inlink channel 50, stores the energy in block 207
and uses this energy to power the tag 15 and transmit data via the
radiative outlink 52. Harvesting of the energy from the reader's
inlink 50 is sufficient to power the tag 15 and its transmission of
the outlink channel 52. In a preferred embodiment, the tag 15
harvests the energy in the inlink signals 50 until it obtains
sufficient energy to transmit a signal to the external reader H
along the outlink channel 52. As illustrated in FIG. 15, this
harvesting process typically is substantially longer than the
duration of the burst information sent out by the tag 15, thus
allowing for amplification of the outlink channel 52 with respect
to the instantaneous power harvested from the inlink channel 50.
For example, if the inlink channel 50 is harvested for 100 ms and
the outlink burst of information is 1 ms in duration, the outlink
power transmission 52 may be 100 times larger than the
instantaneous power harvested by the pill 14 from the inlink signal
50.
Ingestion Detection
[0078] An important aspect in successful detection of the ingested
electronic pills is to positively identify the origin of the
transmission, that is, whether the pill 14 is transmitting from
inside the patient's body 16. Knowledge of transmission origin is
necessary to detect a patient who might intentionally spoof the
system into registering a positive compliance. Multiple
methodologies can be implemented for ingestion detection with
sending element 208. Noting FIG. 17, multiple techniques exist for
"triggering" the system to respond only after reaching the stomach.
The trigger can be activated by the dissolving of material that
opens (or closes) a switch. The trigger can be based on electrical,
chemical, or mechanical detection of stomach or GI tract contents
(e.g., pH sensor. ISFET, temperature sensor, three electrode
electrochemical cell, MEMS, microfluidics, miniaturized or
nanoscale lab-on-a-chip, biomarker targeting, biosensors, optical
sensor, sound transducers, bio- or chemi-luminescent sensor, etc.).
When spoofing is not an issue, the trigger can be activated just
before ingestion or by the reader 11. Additionally, one also
simultaneously measures changes in material properties such as
physical size (swelling), magnetism, polarizability/polarization,
phase (solid-solid, solid-liquid, liquid-liquid, etc.), viscosity,
chemical/molecular makeup, optical clarity, thermal conduction,
state of charge and so forth. In one embodiment, the sensor senses
changes in the outer walls of a capsule, such as temperature or
conductivity before it comes in contact with the outer
environment.
[0079] The ingestion detection system using the galvanic gastric
sensor 284 (FIG. 11) with sensor 208 communicates with the control
subsystem 209 of FIG. 4. The control subsystem 209 is then either
programmed to process the data it receives to determine if the tag
15 is in the proper location, or passes the data through the
transmission subsystem 206 for analysis by the external components,
for example the reader 19 or 111, external device 54, or central
database system or healthcare provider 60. In another embodiment,
the tag 15 does not respond to queries from the reader 111 or 19
until the ingestion detection system 208 indicates that the tag 15
is in the proper location, such as the stomach S.
[0080] Additionally, the presence of specific features in the
received signal from inside the body may be sufficient to determine
the transmission origin. For instance, signal strength in outlink
52 coming from inside the body 16 is lower compared with that from
outside the body due to attenuation from tissue, blood, and bones.
It is also reasonable to expect a shift in the resonant frequency
or a unique characteristic of the frequency spread or content when
a signal propagates through tissue, which is absent when the
transmission is outside the body 16.
[0081] Additional techniques for detecting the origin of the
transmission of tag 15 include:
[0082] 1. The dynamics of pill motion in the esophagus E (e.g.,
speed of pill travel, orientation of magnet, and path of travel)
and or stomach S may provide subtle discriminating differences
between the inlink signal 52 received from tag 15 inside the body
16 and a tag 15 that is outside the body. The peristaltic motion of
the esophagus and the tossing and turning in the stomach may
produce pill motion that affects the signals received due to the
natural or purposely modified directionality of the fields
generated by tag transmission. Additionally, there is a normal
progression from mouth M to esophagus E to stomach S that will
produce a difference in motions that must be obtained sequentially
to validate the location of the pill 14.
[0083] 2. Transmission of unique codes based on a variety of
potential sensors attached to the tag 15. In one embodiment, body
temperature and/or pH sensors are included in the ingestion
detection system 208 and either processed or relayed by the control
system 209 to the transmission subsystem 206. The control subsystem
209 can transmit either raw sensor back to the reader 111 or 19 for
analysis of the patterns, or process the data itself and transmit
back to the reader 19 (FIG. 1) or 111 (FIG. 3) an indication of its
location.
[0084] 3. Ensuring that the pill 14 is only active inside the
patient's body 16. For instance, the pill 14 is inert when
dispensed and is activated upon contact with saliva and/or other
bodily agent.
[0085] 4. Alternatively, the pill 14 is activated outside the body
16, prior to ingestion, and deactivated inside the body 16 after
coming in contact with bodily fluid.
[0086] The activation/deactivation process can be carried out
using, for example:
[0087] 1. Selectively coated sensors that exhibit change in
properties in the presence of specific chemical compounds.
[0088] 2. Biodegradable switches based on proteins that are broken
down when exposed to digestive enzymes in the stomach.
[0089] 3. Unique GI fluid sensors based on the properties of the GI
fluid.
[0090] Conductive sensors. One implementation strategy of a bio
switch is to interface the conductive sensor with a transistor
(e.g., MOSFET, FET, BJT, etc), as shown in FIG. 7. A conducting
sensor in series with resistor R1 acts as a simple resistor divider
and provides the necessary biasing voltage to the transistor gate.
The output of the bio-switch is taken from the transistor drain and
fed to the enable port of the RF transmitter (an RF transmitter is
used as an example, but can be any electronic device that requires
activation). A power source provides necessary power to drive the
transistor and activation voltage. When the bio-switch is outside
the body, the resistance of the conductive sensor is small compared
to R1; thus the activation voltage (VA) will be below the gate
threshold voltage. When the gate voltage is below the threshold,
the transistor is turned off and the voltage at output equals zero.
When the bio-switch comes in contact with a bodily fluid, select
chemical molecules will bind to the conductive sensor and increase
its resistance, thereby also increasing the activation voltage.
When the activation voltage increases beyond the gate threshold
voltage, the transistor turns on, and voltage at output equals that
of the battery. A large voltage at be output in turn enables the RF
transmitter and readies it for transmission.
[0091] An alternative implementation is shown in FIG. 8, where the
circuit configuration yields a deactivation circuit. When the bio
-switch is outside the body, the voltage at output equals that of
the battery; that is, the RF transmitter is enabled. When the
conductive sensor comes in contact with a bodily fluid, the
transistor is turned on and voltage at output equals zero, thereby
disabling the RF transmitter.
[0092] A bio-switch implementation using a conductive sensor is not
limited to the above examples. Variations in transistor type,
substrate type, biasing schemes, selection of power, etc., can
yield several different implementation options. An exemplary
concept here is the utilization of a conductive sensor to drive a
switching mechanism. In the above examples a battery was used to
drive the transistor and circuitry, but instead a charged capacitor
can easily replace the battery. The switch can also be used to
modify the frequency of the signal transmitted or detected
externally (e.g., changing the frequency response of the
pill/antenna). The capacitor can be charged before a pill is
dispensed or can be charged by RF induction as is done in RFID
techniques. One positive aspect of using a capacitor is that over
time the capacitor will discharge and the entire system will become
inert, meaning the subject must take the pill within a given time
frame, thereby increasing the robustness of the system to
spoofing.
[0093] MOSFET sensor. Another implementation of the bio-switch is
to use a MOSFET e-nose sensor instead of a conductive sensor. A
bio-switch with a MOSFET e-nose sensor can be implemented with much
simpler supporting circuitry since the transistor does both sensing
and switching. An example is shown in FIG. 9. The resistor divider
of R1 and R2 provides a fixed activation voltage to the transistor
gate. When the bio-switch is outside the body, the activation
voltage is just below the gate threshold voltage; therefore, the
transistor is off. When the MOSFET sensor comes in contact with a
body fluid, a catalytic reaction takes place at the transistor gate
and changes the channel conductivity; i.e., the gate threshold
voltage is lowered so that the activation voltage is now above the
threshold voltage. Therefore, the transistor turns on, and the
voltage at output equals that of the battery. Again, this
illustration is just one possible implementation scheme, and
variations can be constructed with different types of substrate
(e.g, n-type and p-type) and supporting circuitry.
[0094] An additional embodiment utilizes biodegradable switches
that undergo significant changes in conductivity when exposed to
the digestive enzymes of the stomach. One can mix a conductive
substance (e.g., carbon) with a non-conductive substance (e.g.,
protein). A conductive substance doped with a non-conductive
substance will tend to have lower conductivity (high resistance)
than a pure or even semi-doped material. When the doped material
comes in contact with digestive enzymes, the non-conducting
material is broken down or dissolved by the enzymes, leaving,
behind just the conductive material. One possible switch
implementation can be based on a composition of carbon and albumin.
The albumin protein is broken down by pepsin, an enzyme that is
naturally present in the stomach. When the switch composition is
devoid of albumin, the conductivity of the switch increases and
bridges a gap in the circuit to complete the circuit. A number of
possibilities exist in selecting a conducting material and a
protein. Furthermore, it is also possible to incorporate multiple
non-conducting materials to yield switches that are extremely
selective to activation.
[0095] In the embodiment shown in FIG. 4, the in-link 50 signal is
used for energy harvesting 205 and the in-link signal 50 is
sufficiently low in frequency such that most of the energy is
transferred galvanically through the body of the patient 11, the
tag 15 is only easily powered when the tag 15 is in contact with
the body of the patient 11 since the in-link signal is
significantly attenuated in the air. As such, the tag 15 will not
respond to queries from the reader 11 until such time as the pill
is being touched or ingested by the patient 11. This provides a
level of spoofing prevention with virtually no additional
complexity added to the system.
[0096] Noting FIGS. 10A and 10B, in order to ensure that the pill
is ingested, the antenna system can be disabled by electrically
"shorting" the antenna through the use of an ingestible switch 90
that contains a circuit breaker 92 that becomes modified in the
presence of gastric juice. An embodiment of this concept includes a
method of breaking a circuit via the swelling of the breaker
material in the presence of stomach fluid. The switch 90 comprises
a thin layer of hydrogel 92 partially coated with a conductive
trace 94 such as metal flake or micro-thin metal foil. When the
hydrogel is exposed to low pH liquid, it swells to about sixteen
times its normal size and breaks the conductive trace 94. This
mixture is then coated with an albumin-based layer that will
prevent exposure of the hydrogel to fluids until the albumin is
selectively broken down in the GI tract by either pepsin or typsin.
The preferred mechanism for deactivating the system using an
ingestible switch 90 is to electrically connect the two pads of an
antenna 13, creating an electrical "short". The lower the
resistance, the more power is diverted from the signaling antenna.
By way of example, a five ohm resistance is sufficient to reduce
the input power from the antenna by 95+%. A resistance of 10K ohms
will reduce the input power to the signaling chip by only 10% or
less. In the case where the in-link 50 is separate from the
out-link 52, either antenna can be shorted by this technique,
essentially crippling the tag 15. The preferred embodiment is to
short the in-link antenna in a system that utilizes the in-link to
power the system.
[0097] Sensor such as pH sensors and other chemical sensors are
fairly complex devices. Noting FIG. 11, to avoid a requirement to
embed such a complex device into the tag 15 or integrated circuit
20, the preferred embodiment of a gastric sensor 208 utilizes a
galvanic couple 208 that is placed in various bodily fluids
(stomach fluid, esophageal fluid, GI fluid, etc.) to create a
measurable change in electrical properties such as current,
voltage, and/or resistance and allow digestible electronics to
evaluate the location of a tag 15 in the human body 16. In one
embodiment, the sensor 208 senses changes in the out walls of a
pill 14, such as temperature or conductivity before it comes in
contact with the outer environment. In the preferred embodiment,
the galvanic couple can provide discrimination of location as well
as providing electrical power to the system. The ingestion
detection system 208 on the tag 15 works either outside or inside a
pill 14. Inside the pill, the detection system 208 operates when
the GI fluids permeate the pill or dissolve any external layers.
The tag 15 begins generating power and voltage as soon as it is
wetted by ingestion and allows the tag 15 to begin communicating
with the reader 111. As the tag moves through the GI tract
M,E,S,D,I,R, the sensor or voltage information is communicated or
processed by the control logic 209 such that location information
can be determined by the reader 111 or other external system. FIG.
11 shows the GI sensor/energy cell connected to control logic 208.
The GI sensor requires two electrodes for operation and one or both
of these electrodes may also function as antennas. In the preferred
embodiment, one of the electrodes for the GI sensor comprises a
small strip of metallic zinc while the second electrode consists of
a specially coated silver electrode that is shared with the inlink
antenna.
[0098] In one embodiment, the galvanic couple 284 is constructed of
two differing metals 280, 282 or compounds that, when placed in a
bath of any number of solutions, produces an electric voltage and
subsequent current and is measured by the control system 208.
Metals used for a galvanic gastric sensor 284 are transformed by a
number of chemical reactions to produce a new chemical compound.
The new compound changes the differential voltage. Upon immersion
in a target fluid, the compound transforms into a different
compound and accompanying the transformation is a change in
voltage. Other changes in the galvanic cell materials can be phase
transitions, state transitions, amount of the chemical compound
(causing a natural change in differential voltage based on the
degree of material available to sustain such a voltage), and other
materials transitions that cause a change in the electrical output
of the galvanic cell. In the preferred embodiment, the GI sensor
creates varying degrees of current or voltage depending on the
nature of the fluids in which it is immersed. Thus, the GI sensor
not only gives true/false data about the environment, but may also
senses the chemical/electrical/thermal/etc. makeup of the
environment and give a signal corresponding to the state.
[0099] The metals or compounds are connected to a measurement means
in the control logic 208 (FIG. 11) and can be a voltmeter,
potentiostat/galvanostat, electronic switch or other means to
measure or gauge the voltage and report if and/or when the target
electronic reading is reached in the target solution. If the sensor
284 is not in the target solution, the voltage will not change
appreciably as no chemical transformation will proceed. Thus, the
voltages or an indicator of location can be transmitted via the tag
15 to the reader 11 or 111 to confirm the location of the pill 14.
Such chemicals transformations include silver phosphate and other
silver compounds, including silver chloride, silver sulfate, silver
carbonate, or even silver metal itself. Transformation can occur on
the anode or cathode of the galvanic cell. In the preferred
embodiment of FIG. 11, a silver phosphate electrode 280 is attached
to a zinc electrode 282, and the silver phosphate transforms to
silver chloride and silver metal while the zinc oxidizes to zinc
metal or forms a zinc compound with anions in solution.
Accompanying the silver materials transformation is a voltage
differential (from high-to-low or low-to-high state). The
voltage/current differential is affected by the selection of the
two metals or compounds (or mix thereof), whereby a silver
phosphate-zinc system differs in output voltage/current from that
of a silver-phosphate-copper or silver sulfate-zinc system.
Furthermore, a dissolvable or protective coating 281, 283 may be
applied to the electrodes 280,282 such that the electrodes are not
exposed to the fluid until a certain external condition exists,
such as when the tag 15 is exposed to the high chlorine content of
the stomach. Coatings on each electrode 281, 283 can be the same or
different, providing flexibility in the voltages and currents
produced in different transit times and locations in the body
16.
[0100] FIG. 12 is a chart describing the voltages measured from the
silver phosphate electrode 280 of FIG. 11 formed by applying 9V to
a silver chloride electrode in KH2PO4 solution with a silver
electrode return path 282. The silver phosphate electrode 280 was
tested at loads of 20 kOhm and 1 kOhm. The charts in FIGS. 12A, 12B
and 12C show the time course of voltages of the electrodes with
differing amounts of phosphate (exposure time to the KH2PO4
solution), differing loads, and differing solutions. The gastric
sensor 284 has a substantially different voltage in HCl, the
primary component of stomach fluid, versus sulfuric acid
solution.
[0101] In alternate embodiments, the tag 15 is modified to include
sensors to provide the ability to access the tag's internal memory.
For instance, the tag 15 can have a pH monitor, temperature probe,
or other sensors 42 (FIG. 2C) to verify compliance. In addition, it
may be beneficial to use a system that can also provide a readout
of the signal strength. This signal strength is beneficial for
optimizing the communication protocol dynamically as well as
providing potentially discriminating information relating to the
location of the tag 15.
Biometrics
[0102] In addition to determining when the pill 14 is ingested and
where it resides, it is important to detect that the pill is
ingested by the appropriate person. As such, a variety of
biometrics are utilized to detect that the reader 111 and/or pill
14 are located on or in the correct person 16.
[0103] In one embodiment, an electronic pill monitors physiologic
signals inside the body 16 that are typically difficult to mimic
outside the body. For example, the patient's electrocardiogram
(ECG) is detected and measured by the electrical contacts or
antenna of the tag 15. The tag 15 either processes the signal or
passes the signal via the outlink 52 to the reader 11 for further
processing. Detecting the presence of a valid ECG signal indicates
that the tag 15 is inside the body 11. Detection of a periodic
pulse between 30 and 120 BPM is sufficient to detect that the tag
15 is inside the body. Furthermore, a wide variety of parameters
can be extracted from the physiologic signals detectable inside the
body 16. In a preferred embodiment, the processing system (either
in the tag 15, reader 11, or elsewhere downstream) detects
parameters of the electrical characteristics of signals received
inside the body 16 including but not limited to: periodicity,
amplitude, signal shape (including peak geometry, relative height),
and signal to noise ratio. In addition, the signal detected inside
the body can be transmitted to the reader 11 and verified against a
preloaded signature of the ECG or other physiologic signal recorded
earlier, for example, during the initial administration of the
system 10. Additionally, the reader 11 can record the same signal
outside the body 16 and ensure that the tag 15 is in the same
person 11 that is wearing the reader and also checked against the
stored signature. These features of the ECG and other physiologic
signals measured at the tag 15 or reader 11 are also capable of
biometric identification.
[0104] These physiologic features and their dynamic features
(changes in the signals over time) are useful to identify the
patient 16, ensure ingestion, or determine the location of the tag
15 in the digestive tract M,E,S,D,I,R. The dynamic features include
but are not limited to heart rate variability, changes in signal
strength as the tag moves through the body 16 and muscle activity
in different parts of the body. For example, the ECG will be quite
strong as the pill passes the heart in the esophagus E and then
gradually get weaker as it moves farther from the heart in the GI
tract S,D,I,R.
[0105] In an embodiment, the external reader 11 is used to monitor
and assess a given patient's 16 ECG output (periodicity, peak
geometry). This information is used for a first calibration step
and recorded as the baseline ECG output. The later measurement of
the ECG by the reader 11 validates that the same person is using
the reader. Additional, the measurement by the tag 15 can be
checked against this calibration to ensure that the proper person
is taking the medication. In this case, if either the medication or
the external reader is switched to a different person 16, the
results can be checked against the calibration data. Calibration
can take place in the presence of proper supervising personnel,
including doctors, nurses, etc., and the calibration can be locked
to those who either have calibration codes or calibration
devices.
[0106] These biometric capabilities can also be used to help guard
against improper medication (type or dose) being taken. Each tag 15
can be programmed to be taken by a specific patient. The patient
specificity will be recorded by certain physiologic signals that
can identify individual patients, such as parameters of the ECG.
The reader 11 or interface 54 can first be programmed to register
the kind and frequency of medication to be taken for a given
patient ECG. The reader 11 or interface 54 then alerts the patient
or proper personnel if the medication taken was given to the wrong
person (pill ECG does not match reader ECG) or if the medication
was taken at improper time intervals (over- or
under-medication).
Control Logic/IC Design
[0107] Maximizing power efficiency is of utmost importance to
maximize the reading distance between the reader 11 and the tag 15
as well as power output and detectability. Advanced low-voltage and
low-power circuit design topologies and a suitable process
technology are required to achieve operation with small input power
levels from radiated electromagnetic fields.
[0108] Referring to FIG. 13, the preferred embodiment of the
integrated circuit 20 for the tag 15 includes: protocol logic 306
having a random bit generator XXX for robust two-way communication
and control, data acquisition subsystem 304 and sensor 314 to
determine the strength of the in-link signal 50, inlink subsystem
302, outlink subsystem 308, and energy harvesting and storage
system 310. The IC 20 is designed with fallback operating modes,
including a chirp mode and a beacon mode. In the chirp mode, the
protocol is suspended and the IC 20 transmits data whenever it has
sufficient power from the energy harvesting and storage system 310.
In beacon mode, the IC 20 transmits a periodic burst pattern with
no data (bypassing all digital logic). In one embodiment, the
energy harvesting and storage system 310 extracts power from
induced currents generated from the external reader 11 via the
inlink subsystem 302 or directly via the inlink antennas 50. In a
second embodiment, a galvanic cell, GI sensor, thermocouple, or
other method of generating power from the digestive tract
M,E,S,D,I,R or motion through it provides primary or supplemental
power via the energy harvesting subsystem 310 to enable the IC 20.
The outlink subsystem 308 drives the outlink signal 52 under
control of the protocol logic and control subsystem 306. The
protocol and control system 306 contains all the logic to control
the IC, the communications protocol, the data acquisition,
synchronization, and data storage and output, including the
preprogrammed information about the medication, patient, study and
other information. Minimizing the power usage of all these
subsystems and in particular the outlink subsystem 308 is of utmost
importance.
[0109] Preferably, the IC 20 is fabricated using industry standard
CMOS manufacturing processes in class 10 or better clean rooms. The
physical dimensions of the IC 20 are expected to be very small,
less than 1 mm.times.1 mm.times.0.1 mm. When affixed to the tag 15,
the IC 20 is encapsulated in biocompatible epoxy to cover any hard
edges and to prevent interaction between the IC 20 and the
patient's body 16. The preferred IC 20 is a custom designed
microchip that stores the medication information, reads the GI
sensor, and implements the signaling and communications protocol.
The IC is designed to operate with extremely low power and to
provide reliable deep in vivo communications.
[0110] In addition to integrated circuit implementations for the
various logic and systems of the tag 15, another embodiment
includes printed electronic circuits created with various inks
including metallic, dielectric, and organic materials. The creation
of complex printed electronics requires the creation of multilayer
electronic devices such as transistors and capacitors, silver
conductive ink and dielectric materials are typically loaded into
separate ink cartridges. For example. In the case of capacitors,
fabrication can be achieved by first printing a single line of
nanoparticles onto a substrate that is heated until the inks are
metalized. Next, a dielectric of polymer is printed directly over
the line. Finally, a second conductive line is printed
perpendicular to the original conductive line. In this way, the
overlapping cross-section of the two conductive lines--with a
dielectric between them--creates a capacitor whose capacitance is
defined by the overlap area and the dielectric material and
thickness Thus, if an antenna is printed simultaneously and
attached to each conductive line, a simple 3-step inking procedure
is enough to begin creating simple inductor-capacitor antennas that
can resonate at a tuned frequency.
[0111] Many generally recognized as safe (GRAS) materials are
available for use as dielectrics, for example
polytetrafluoroethylene (PTFE), polyimide (from precursors) and
PVP. In the preferred embodiment, enteric coatings are used as a
dielectric material.
Communication Links and Protocol
[0112] Transponder Antenna Size and Efficiency. The radiation
efficiency of a typical loop antenna increases with loop area and
is inversely proportional to the excitation signal wavelength.
Since the loop area is limited, it is desirable to operate at
higher frequencies to improve the antenna efficiency. In typical RF
applications, operating at higher frequencies can improve the
aperture efficiencies of small antennae to maximize the received
power. However, in biological systems, the operating frequency is a
tradeoff between increased path loss in tissue and antenna
efficiency. Indeed, RF signal attenuation behavior of the inlink 50
and outlink 52 in bodily fluids and body tissue to and from an
ingested tag 15 is complex and difficult to model.
[0113] The tag 15 may be coded with a variety of information
including but not limited to data about medication, the patient 16,
the reader 11, or the drug trial the patient is participating in.
Additionally, the tag 15 can have a unique ID that is utilized with
a database of other information tagged to each tag ID to obtain
similar information without storing it on the tag 15. Upon
detecting the tag 15, any of the readers 11, 111, 211 or 311 can
store a time-stamped reading of a medication event. If the tag 15
is not detected, failed compliance can be signaled, for example, to
the patient 16 and/or to a second party such as a health care
provider or other agency 54 via input and output signals 56,
58.
[0114] It is preferred that the communication between each reader
11, 111, 211 or 311 and the tag 15 provides two way communication,
with the communication from die reader 11 to the tag 15 being
preferably through a conductive in-link channel 50 and the
communication from the tag 15 to the reader being preferably
through a radiative out-link channel 52. The in-link channel 50 is
preferentially in the range of 1-20 MHz; this frequency range
produces efficient data transfer from outside the body to deep
inside the body 16 and can travel through the body galvanically,
requiring very small antennas or pads only to receive the signal.
Because the inlink transmissions 50 travel galvanically, the
signaling attenuates very rapidly outside the body 16 thus
providing for increased privacy for the inlink channel 50. Skin
surface contacts with the reader, as readers 111, 211 and 311,
maximizes the efficiency of the in-link transmission 50 from the
reader. The in-link channel 50 communicates a variety of
information to the tag 15, including but not limited to querying
for the presence of the tag 15, turning the tag's transmitter on or
off, collision avoidance, and various other protocol-based
communications. The inlink channel 50 also provides synchronization
signals between the reader and tag 15. Synchronization between the
reader 11 and tag 15 are particularly important when the outlink
signal 52 is very small (as is expected when coming from inside the
body) and/or when the outlink signal is transmitted in very short
bursts for better energy efficiency.
[0115] In an embodiment, the tag 15 is powered using the RF energy
received by its coil or antenna or in another embodiment where
power is generated by energy harvesting means. As described
previously, this power can be stored temporarily and then used to
transmit a pulse or signal to the reader 11. Storing the energy
internally in the tag 15 helps alleviate two distinct problems.
First, it allows for the storage and amplification of the
instantaneous power received from the inlink 50 or energy input 312
to create higher powered but shorter bursts of outlink
transmissions 52. Second, when transmitting into the body 16, the
external powering signal (inlink 50) creates significant noise that
may make detection of the outlink signal 52 from the tag 15 very
difficult.
[0116] One method to create more detectable signals for outlink 52
is to utilize different frequencies for power transmission and data
signaling. This allows the external receiver 12 of the reader 11 to
be frequency-isolated from its transmitter. A frequency selective
filter may then remove the noise from the transmitter to allow for
high quality reception of the data signal. Lower frequency signals
typically have lower losses in the human body. As such, the power
transmission signal 50 may necessarily be lower in frequency than
the data transmission signal 52 which can be much lower in
power.
[0117] Another method involves the use of dual antennas on one or
both of the tag 15 and receiver 12; that is one antenna or set of
probes/contacts for the transmission/reception of the in-link or
power transmission, the other for transmission/reception of the
data signal.
[0118] As discussed in greater detail below with reference to FIGS.
15-18, another method involves the time multiplexing of the signals
such that the power transmission ceases during predefined time
periods to allow tag 15 to start transmitting data. The circuitry
of tag 15 can be designed to utilize this cessation of power
transmission as a marker to determine when to start transmitting
data. Additionally, that circuitry may store the power during the
"power cycle" for a period of time typically longer than the
transmission cycle to provide a power multiplication to improve the
signal strength of the data transmission.
[0119] It is preferred that the communications to and from the tag
15 and to and from the readers 11,111, . . . are protected,
encrypted, encoded, or made secure in a way to prevent
interpretation by other devices and have software and/or hardware
required to protect the data and support privacy or data security
requirements of the communication system.
[0120] Although the technology described above focuses on RF
technology, many other technologies are possible. The passive
devices that are detected via an external sensor can include many
standard imaging technologies such as X-ray, ultra-wide-bandwidth
(UWB) imaging, ultrasound, or MRI devices. Each can have a
transmitter that transmits energy into the body and detects
reflections or distortions in the magnetic field caused by the
presence of the pill (or pill contents or coating).
[0121] Many of the tag 15 embodiments support IDs and other stored
data that can be transmitted back to the reader 11 via the outlink
channel 52. IDs and other data can be transmitted via pulsatile
signals (information in the pulse duration, pulse spacing, pulse
frequency, etc.) or via digital encoding. To increase
signal-trot-noise ratio, it is preferable to have a
transmit/receive event wherein the tag 15 responds to a request
from the reader 11 with a predetermined signal. This signal is
repeated and then synchronously averaged over multiple
transmit/receive events to produce a better signal-to-noise ratio.
Synchronization of the transmissions from and to the reader 11 and
tag 15 also improves the ability of the reader 11 to detect faint
signals 52 from the tag 15 in the body 16.
[0122] An embodiment of an efficient communication and protocol
approach is demonstrated in FIG. 14. The approach is based on a
unique communication path between the tag 15 and the associated
reader 11. The reader 11 transmits data to the tag 15 by way of the
conductive or galvanic in-link 50 communication channel. The tag 15
transmits data to the reader 11 through the out-link radiative
channel 52. An electromagnetic transmitter block 320 provides the
interface to the radiative channel 52 at the tag 15 and a
corresponding reader RX 322 extracts the signal at the reader 11. A
tag 15 for a patient 16 is linked directly to the patient reader 11
similar to a key and lock. Only data with the proper key or data
word arc recognized by the reader 11 as valid patient data. As an
extra measure of protection, the out-link TX carrier 320 is phase
locked to the reader in-link signal 50 to provide means for
synchronization of data. Phase lock also allows coherent detection
of the tag data at the reader 11, thereby enabling use of phase
modulation and reduced error rates. Since the in-link signal 50 is
propagated by direct body contact (in-link conductive channel),
only the reader 11 attached to the patient's body 16 can properly
demodulate the return tag outlink 52 data. This feature makes
external eavesdropping of the data very difficult. Hence, this
approach enhances security of the data. As will be appreciated,
this communication protocol also allows several tags to be consumed
and data read without the need for individual tag identification
bits, thus reducing significantly the amount of data that needs to
be stored.
[0123] The protocol is composed of the communication link timing
and the associated in-link 50 and out-link 52 data fields. FIG. 15
depicts the relative communication link timing of the data or the
in-link 50 and out-link 52. The process begins with the reader 11
sending an FM modulated signal, or "in-link header" 330 to the tag
15 with information necessary for proper tag operation. The header
is sent periodically every T seconds. On ingestion, a random bit
generator in the circuit 20 for the tag 15 begins operation. On
completion of the in-link header field 330, the value of the random
bit generator is latched. This latched value is used to set the
time, t.sub.o at which the tag 15 responds to the reader 11 by
sending a data burst 332. The data burst 332 contains a subset of
the data stored on the tag 15 to be sent to the reader 11. Several
bursts 332 in sequence make up the full data transmission through
out-link 52. The latched random generator value becomes the pill ID
or address for this specific tag. Since the ID is random, each tag
swallowed will have a unique ID. As will be appreciated by those
skilled in the art, the algorithm may be as simple or complex as
necessary to assure no two tags randomly end up with the same
address. Each tag swallowed will send a pulse 332 delayed in time
from the end of the header 330 proportional to the value of the
random address. In this fashion, no two tags 15 can transmit at the
same time, thus preventing interference but also allowing multiple
ingestion of tags. Also, since the tag address is set randomly,
there is less need for special tag identification bits to be stored
on each tag, thus reducing significantly the number of bits of
memory required on the tag 15. This reduces cost and complexity of
the tag 15 significantly.
[0124] Referring to FIG. 16, a representative efficient inlink data
field 342 and corresponding definitions are shown. Field selection
can be used to improve the robustness of the communications between
the reader 11 and the tag 15. For example, the field N defines the
number of data bursts 332 that the tag 15 uses to define a single
tag information bit. Thus, it is appropriate to use a mechanism by
which the system 10 assigns more data bursts 332 per bit for
situations where the signal to noise ratio may be poor (very large
patients for example). This allows for more integration time and
improved reliability. Such a system is adaptable for broader
[0125] Referring to FIG. 17, a representative efficient outlink
data field 352 is configured to allot two data bursts 332 for a
single bit 354. Depending on the total number of bits J of
information transmitted, N.times.J data bursts are generated. For
example, if the total number of bits 354 is J=16 and N=2, then 32
data bursts 332 are transmitted. As a further example of the
utility of this protocol, the reader 11 may be preprogrammed to
only accept outfit data with the proper patient ID. This along with
the fact that the data is coherently linked to the reader 11
essentially reduces the likelihood of data not associated with this
patient 16 being received as valid data.
[0126] FIG. 18 shows the timing for the case of three tags taken
together to further illustrate the efficiency of the protocol. Tag
1 362 transmits at a random slot after the inlink header 330 and
transmits multiple bursts 332 per bit 354. Similarly, Tag 2 364 and
Tag 3 366 transmit their multiburst per bit transmission in
different time slots after the inlink header 330.
[0127] As has been previously discussed, a communication network
utilizing a phase based modulation scheme is known to have
advantages of reduced hit error rate (BER) for the same
transmission power compared to simple modulation schemes such as
Amplitude Shift Keying (ASK). Since power is extremely limited in
in-vivo communication systems, minimizing BER is a challenge.
Implementing a phase-based modulation scheme requires that the
reader 11 be able to coherently demodulate the signal 52 for each
tag 15. This normally requires that the frequency stability of each
tag 15 be within a tight tolerance (20-40 ppm) to permit the reader
11 to phase lock and demodulate the received signal. Such frequency
tolerance requires that the tag 15 transmit frequency be based on a
crystal reference. Size and safety constraints prohibit the use of
crystals to generate the transmit signal for the tag 15. Further,
since the tag transmission burst is short in duration, there may be
issues in proper settling which may cause demodulation errors.
Another solution is for the reader 11 to have an independent
receiver for each tag 15 and preferably use a phase lock loop based
approach to lock to the incoming signal. There are issues with this
approach as well. First, the burst durations are short making the
design of such a receiver extremely difficult. Second, the tag 15
still requires some measure of frequency tolerance to assure
regulatory or system specifications are achieved. This may require
the need for tag frequency trimming which adds to the manufacturing
and test costs of each tag 15. Hence, a method is required to
eliminate the need for a tight frequency tolerance on the tag 15 as
well as a complex reader 11 receiver design.
[0128] A preferred approach takes advantage of the fact that the
reader 11 is connected via the conductive inlink 50 communication
channel to each tag 15. Hence, by using the reader 11 as the
initial frequency reference and locking each tag 15 to the
reference signal fbr reader 11, a self-synchronized coherent
communication system is realized. FIG. 19 illustrates this concept
in detail. First, the reader 11 generates a reference signal (shown
here for example with frequency of 4 MHz). This signal is passed to
the conductive channel 50 through an interface circuit 372 and
propagated to any tag 15 within the channel. At the same time, the
4 MHz reference 376 is frequency multiplied within the reader 11 to
the tag 15 burst frequency (400 MHz by way of example). This signal
is ultimately used to coherently demodulate data from any tag 15.
In the tag 15, the 4 MHz reference frequency is extracted,
amplified and passed to the input of a PLL demodulator and TX
carrier generation circuit (TAG PLL) 374. This circuit has several
modes of operation including the tag burst mode. During the tag
burst mode, the signal is frequency multiplied to the TX frequency
of 400 MHz. This signal is subsequently passed through the outlink
52 channel where it is extracted at the reader 11. The reader local
oscillator 378 derived from the original 4 MHz reference is used to
demodulate the received tag signal 52. The system is self coherent.
Thus, the tag 15 achieves a tight transmission frequency tolerance
by virtue of the phase lock loop 374 and does not require any
internal crystal reference.
[0129] Other advantages of this embodiment may be seen by referring
to FIG. 20. This figure shows the timing relationship between the
inlink 50 and outlink 52 burst signal and defines the three modes
of operation of the TAG PLL 374 network. The inlink data is sent at
a periodic rate of T seconds, typically on the order of 1 ms. As
described earlier, the tag 15 responds some time later (less than 1
ms) with a TX burst. The TX burst also repeats at the same 1 ms
interval. A single period is expanded in FIG. 20 to further
highlight the modes of operation of the TAG PLL. The TAG PLL
operates continuously. During mode 0 382, the reader sends a fixed
reference signal of frequency Fref (4 MHz). The TAG PLL locks to
this frequency and remains locked until progressing to mode 1 384.
During mode 1, the TAG PLL remains locked; also during mode 1, the
reader 11 frequency modulates the 4 MHz reference signal with any
required information or configuration data for the tag 15. Since
the TAG PLL is still locked to the reader signal, the modulated
data can directly be extracted from the VCO control voltage 375 on
the TAG PLL. Hence, during mode 1 384, the TAG PLL is acting as a
demodulation block. The TAG PLL then returns to mode 0 382 and
stabilizes. Finally, during mode 2 386, the PLL is given the
command to frequency multiply the 4 MHz reference signal,
generating the 400 MHz TX burst signal. This is an efficient
realization using the same circuitry for both inlink demodulation
and TX carrier generation.
[0130] FIG. 21 shows more detail of the TAG PLL 374. One key to its
operation is the dual frequency VCO 392. During modes 0 and 1, the
VCO 392 operates at 4 MHz. During mode 2 the VCO 392 is switched to
400 MHz (with VCO gain parameters changed accordingly) at the same
time a divide by N (100 for this example) is enabled within the
loop. The frequency of the phase detector 394 remains unchanged and
the loop dynamics remain the same. As a result the loop quickly
settles to a precise 400 MHz and the TX burst is transmitted. Once
the TX burst 332 is sent, the PLL 374 is returned to mode 0 and the
process repeats.
[0131] It will be appreciated by those skilled in the art that this
implementation has several advantages. Using fine lithography
integrated circuit technology, the power requirements for the VCO
392 during mode 0 and 1 are very minimal. Simple ring oscillator
approaches may be used for the VCO 392 requiring just a few
micro-amps of current. This allows the TAG PLL 374 to operate
continuously which then permits a very frequency tolerant
transmission burst. The TAG PLL 374 will stabilize with each
subsequent burst. The same circuitry is used for both transmit and
receive and area requirements are very small leading to a low cost
solution,
Attachment (inside, Outside, Both; Premade Built in, Attached)
[0132] Wrapped tag embodiments are shown in FIGS. 5A and 51B.
Noting FIG. 5B, the wrapping process is typically partially around
or completely around the outer surface of capsule 46, soft gelcap,
or other medication carrying device as shown in FIG. 5B. The resent
invention also includes the method of attaching the tag 43 to the
inside surface of the capsule 46 as shown in FIG. 5A.
[0133] Referring again to FIG. 5B, to avoid the accidental or
purposeful removal of the tag 43 from the outside of the capsule
46, avoid damage to the tag from handling and environmental issues
and to increase the aesthetic appeal of capsules (and minimize
patient hesitation in taking an electronically-tagged medication),
it is prudent to conceal all electronic devices, including antenna
44 and chip 47, inside an opaque or mostly opaque gelatin capsule
while maintaining communications to various body-dependent sensors
or electronic devices. Inconspicuous leads that lay flat on the
surface of the gelatin capsule 46 are likely to be of little
indication of the presence of a more complex antenna-chip structure
within the capsule 46.
[0134] Now noting FIG. 5A, further placing the tag 43 inside the
capsule 46 maintains a minimal change in capsule volume, and
simplifies tag attachment and functionality. Referring, to FIGS. 22
and 23, a trace or foil 49 that runs from inside the gelatin
capsule to its exterior allows for electronic transmission from
within a capsule or power harvesting from outside the capsule. The
exposed antennas or leads 79, 44, 81 on the tag 43 make electrical
contact with the interior-exterior lead 49 on the capsule 43. The
interior-exterior lead 49 is preferably constructed such that an
elongated pads 86,87 are included to make contact with the antennas
or leads 79,44,81 of the tag 43. The tags are constructed with
coatings such that only the leads or antennas that need to be
connected to the interior-exterior leads are exposed while all
other electrical components and antennas are coated in a protective
and/or dielectric substance. To make the interior-exterior
connection, the metal film 49 is thin enough to allow a 2-part
gelatin capsule to still snap together. The tag 43 itself, being
composed only of thin components (antenna, chip, substrate, etc.),
takes up a minimal amount of volume within the capsule 46 and
should not impair drug loading amounts.
[0135] When the pill 14 is in the form of capsule 17, an
alternative method is to place the tag 15 inside the capsule and
allow the tag to work normally after the capsule begins to absorb
fluids. A tag 15 using leads that make contact with the interior
wall of the gelatin capsule 17 and activate upon wetting of be
capsule can react with the environment to identify location,
chemistry, or otherwise. The system 10 can then use the gelatin
capsule itself as a protective system in non-aqueous environments.
The diffusion time of fluid through the capsule wall is the
limiting factor for detection of body fluids or
transmission/reception of signal within the body itself. To make
contact with the outside environment in an expedient manner,
however, the receiving pads must be in direct contact with the
capsule as sonic pills simply swell outwardly. Thus, for this
approach an adhesive for attaching the tag 15 to the inside wall of
the capsule 17 is required. This will help prevent tampering,
prevent misfiring of the pill 14 in beverages or other liquids, or
other problems with proper antenna function as there are no
external leads whatsoever. Destruction of the pill 14 and its
contents is then necessary to access any electronics.
[0136] In most cases, placing the tag 15 inside the capsule works
well. In some cases, the delay between ingestion and activation of
the sensor system on the tag 15 when using a gastro-intestinal
powering system may be problematic. Fitting the tag 15 with
external exposed sensor or pads would be advantageous for quick
analysis of the body environment for advanced location discernment.
Transit from mouth to stomach typically takes place in less than 8
seconds, which is faster than most gelatin capsules can absorb
fluid and begin to break down. Having an external lead minimizes
this delay in sensing time for an internally-placed tag 14. The
number of pads that need to be exposed can be as few as one,
depending on configuration.
[0137] Noting FIG. 23, in one embodiment, the tag 43 has a chip 47
with a high frequency antenna 47 and a low frequency antenna 79,
both deposited on a biocompatible substrate 45 that fits inside a
gelatin capsule 17. Leads 78 on the antenna 72, 73 are exposed to
make contact with the external pads 80 surrounding the capsule 76.
This embodiment also allows fbr "hot-swapping" of internal and
external components of the tag 70. Different geometric designs of
an external antenna can be accommodated by an internal tag by
creating a system that simply needs "lining up" of antennas with
external traces. This way, a number of antennas/sensor probes can
be produced that have specific applications (frequency, power
transmission properties, size, complexity) for a specific drug,
creating a modular design that can have certain unique or complex
components placed on the exterior of the capsule 17 and maintain a
communication pathway. This also prevents the need for adhesive
backing for the internal portion of the tag 70 if the elasticity of
the substrate 74 provides sufficient rigidity to hold the tag 70 in
the proper location. Additionally, the internal tag 70 can be
created on a flat substrate as described earlier, but the external
portion of the tag may be sufficiently simple to be printed,
built-in, or otherwise attached to the outside of the capsule 76.
This embodiment also makes the process of creating multi-metal
antennas or sensors simpler as only small strips of material need
be placed on the outside of the capsule 70.
[0138] In another embodiment, the gastric sensor or other leads
that are exposed to the outside of the capsule 76 are placed on the
surface of the inner half 76A of the capsule, the portion to the
capped by the other half 76B. The antenna 72 is then wrapped around
the capsule 76, with the exposed antenna leads making contact with
the metal extensions on the capsule's inner half 76A (see FIG. 1).
In this way, the tag 70 itself is concealed and only two very small
metal strips are exposed, improving the appearance of the capsule
76.
[0139] Referring to FIG. 24, be internal component of the tag 43 is
inserted into the cap of the capsule and slides over the antennas
44, 79 printed or affixed to the smaller diameter portion of the
capsule. When the tag is inserted into the smaller diameter portion
of the capsule, via's or through holes 80 are punctured into the
capsule to allow connection from inside to outside the capsule when
necessary.
Tag Construction
[0140] Referring to FIGS. 25 and 26, in the preferred embodiment,
the main components of the tag 15 are a very small integrated
circuit (IC) 71, a metal antenna 72, a gastrointestinal (GI)
sensor/energy cell composed of a specially coated GI sensor pad
that doubles as an inlink antenna 73 and a second metalic GI sensor
pad 75, and a substrate 74.
[0141] The substrate 74 is composed of a specially coated paper.
Non-whitened, low-weight papers are non-toxic and become softened
in the GI tract M,E,S,D,I,R to allow for easy passage without risk
of lodging as it passes. These papers will then be coated with a
pharmaceutical enteric coating known as "Eudragit", which provides
a smooth surface to allow printing of antennas. Eudragit is also a
pH-sensitive material that will dissolve in the colon R, allowing
the tag 15 to remain active long enough to be detected before
disintegrating.
[0142] The biocompatible antennas 72, 73 are printed on the
substrate and preferentially coated with Eudragit as described
above to protect the antenna and prevent interaction with the
antenna materials until the tag passes into the colon R where it
begins to disintegrate.
[0143] The GI sensor/energy cell includes the use of a zinc
electrode 75 and silver electrode 73 with special coatings as
described previously. The GI sensor is designed to restrict the
bioavailability of the materials to levels far below FDA, EPA,
and/or recommended daily intakes. The simple GI sensor produces
induced voltages from the voltaic battery when different metals
interact with the acidic GI fluids. Zinc foil is preferably used
for small scale production and is bonded to the tag 15 using a
conductive adhesive. An analog to digital converter within data
acquisition block 304 in the chip 20 is used to uniquely detect the
sensor's response to GI fluid.
[0144] FIG. 26 shows the preferred embodiment of the tag, its size,
and its approximate location of features. The tag 15 consists of
four logical components: the tag body interface 73, the GI sensor
75, the tag integrated circuit (IC) 71, and the out-link TX antenna
77. The tag body interface 73 includes two in-link 50 pads (body
contact pads) that are 1-2 mm by 4mm. The GI sensor includes a pad
75 that is approximately 1 mm.times.5 mm. The out-link antenna 77
utilizes the rest of the available space. The tag IC 71 is shown in
the inlay of the figure. FIG. 26B represents the tag after it is
wrapped around a cylindrical object. The in-link antenna pads are
separated by the maximum available distance, which is 180 degrees
across the capsule once the tag is wrapped around it. The out-link
antenna is optimized for the required three dimensional geometry of
the capsule (or pill) after attachment. The tag 15 materials and
construction conforms to all safety, regulatory, and manufacturing
requirements. The physical structure of the tag 15 and its
relationship to a medication capsule is shown in FIG. 27. Target
Tag sizes are shown such as to conform to a size 0 capsule. Future
generations are expected to support smaller capsule geometries and
tablets.
READER
[0145] To Minimize the size and power requirements of the external
reader 11, in one embodiment it may not include the capabilities to
transmit information via a cell system, wi-fi, or other wireless
network. However, in another embodiment, the reader 11 can transmit
data to a standard cell phone, pager, or other device as shown in
FIG. 1 and as described below with reference to FIG. 3, to allow
for real-time updating of patient compliance and monitoring. Using
a two part reader system allows for a miniaturized on-body receiver
19 and a more powerful mobile device 54 with a more sophisticated
user interface for messaging and transmission to a global database.
In such a two-part reader system, an on-body reader 11 has two
communication systems, one 50, 52 to communicate with the tag 15
and one 56, 58 to communicate with the mobile device (for example a
bluetooth; see FIGS. 3 and 30 and discussion below). In such a
system, the mobile device only requires special software to operate
as both a standard mobile device and a front-end user interface and
wide area network (WAN) transmission interface.
[0146] The external reader 11 can be embodied in several forms. For
example, the reader can be the wristband 111 of FIG. 28, or the
patch 211 of FIG. 29 that can be adhered to the skin like a
bandage, an arm band, a handheld device or the like. In some
embodiments, it is advantageous for the reader to have contact with
the skin during a medication event. It is also advantageous to
design the reader to be readily available and/or worn to ensure it
is present with the patient 16 for all medication events. Another
form is the pill container 311 shown in FIG. 30 with contacts 313
on the bottle holder 311 for skin contact during the ingestion of
the medication. A minimal user interlace exists on the bottle
holder 311 with a button to indicate ingestion has taken place 312
and an indicator 313 to determine when the pill was detected. The
patient 16 removes the medication from the container 311, ingests
it, presses button 312 and holds the pill container 311 against the
skin until the ingestion event is detected at the contacts 313 and
the indicator 314 confirms that the tag 15 was detected in the body
16. In other forms, the reader is also built into a mobile device
such as a cell phone, PDA, wrist watch, or into a memory card,
dongle, or other add-on device that can be attached or inserted
into a mobile unit.
[0147] Noting FIG. 30, each, reader 11, 111, 211 and 311 has a
small user interface 227 that presents indicators of ingested
medication being detected and/or the capabilities to indicate when
medication should be ingested. The readers are disposable or
reusable, or contains portions that are disposable and reusable.
The readers also preferably contain means for storing the recorded
data for downloading via USB or other means directly to a PC or
other computing device. The readers are also preferentially
rechargeable. In addition, for those applications where the readers
do not need to be mobile, they may be built into a dongle or other
means into a standard computer or laptop.
[0148] Continuing with FIG. 30, the reader comprises several
RF/analog front-end components interconnected with a digital
processing core to handle the communication protocols. The body
interface or antenna subsystem 220 interfaces with the body 16 or
media surrounding the body (e.g., air). It contains the antenna and
or contact points to transmit the inlink 50 data to the tag 15 and
receive the outlink 52 data from the tag 15. In addition, the body
interface subsystem 220 includes the sensors, contacts, or antennas
necessary to acquire physiologic or biometric data required to
ensure the reader 11 is on the right patient 16 and the tag 15 has
been ingested by the right patient. The receive subsystem 221 and
transmission subsystem 222 contains the electronics to drive the
antennas and/or receive data from the body interface and antenna
subsystem 220. The uplink receive 225 and uplink transmit 226
subsystems transmit data to and from an either a mobile device for
wide area communication or directly to a wide area communication
system such as cell phone, wifi, or paging networks. The protocol
and control subsystem 224 manages the communications of the outlink
52, inlink 50, uplink 56, and downlink 58 transmissions, controls
the user interface 227 and processes all data coming in and out of
the reader 11. The user interface system 227 provides information
to the patient about when a tag 15 has been detected, allows the
patient 16 to initiate a manual detection, provides indicators of
when the pill 14 should be taken, and provides other information to
the patient.
[0149] The transmission subsystem 220 consists of a multiple
modules. The first module contains a high voltage modulator stage
with a programmable low frequency carrier to galvanically couple RF
signals into the body 16. The supply voltage of the modulator can
be dynamically varied to superimpose in-link telemetry data to
communicate with the tag on the pill. Digital input signals will be
derived from the protocol and control subsystem 224 tasked to
handle communication protocols to and from the tag and also to and
from an uplink/downlink transceiver 225, 226 that wirelessly
interconnects mobile devices to the reader 11. The second module is
a UHF receiver chipset used to demodulate out-link 52 data from the
tag 15. The receiver is used to downconvert the detected out-link
RF signals 52 for data extraction by the baseband processor.
Preferably, all communication protocols between reader 11, tag 15
and mobile devices 54 are synchronized to a master clock generation
module to ensure proper timing control.
SOFTWARE SYSTEM
[0150] True adherence improvement is likely to only be achieved
when the patient 16 is motivated to follow the prescribed regimen.
By connecting the patient with the medication, the pharmacodynamics
(PD) and pharmacokinetics (PK), dose/response data, and their own
reaction to the medications, patients become more interested in
their regimen and become more adherent. The software system is
preferentially implemented in a smart phone application that is
linked to the reader 11 and the information provided by the
uplink/downlink data. In a preferred embodiment, the software shows
estimated blood levels of the drug of interest based on the known
patient information and medical information stored in the system,
as well as the exact timing and doses of the medication taken by
the patient. The software shows the patients how missing doses or
improperly taking their medication affects their simulated blood
levels, drug effectiveness, and how it changes their physical
responses to the medication.
[0151] Other embodiments include personalized calendars that a list
each medication and dosage listed under the following 4 times
periods: Morning, Noon, Evening, and Bedtime. If a patient does not
take their medicine, they are asked to write the reason. It also
lists any special instructions to help prevent adverse effects
resulting in decreased medication adherence. The software also
contains a list of abbreviated instructions on how to use and
monitor each drug so that the patient understands the benefit and
risk of each drug. The software also allows the pharmacist to enter
how many days late the patient comes to the pharmacy for a refill
of chronically taken medication. If the adherence rate is
unsatisfactory, the pharmacist is presented with various options on
how to enhance adherence through patient education programs
designed from well documented motivational interview
techniques.
[0152] The Personalized Medication Adherence Registry (PMAR) is a
mobile software system that receives medication adherence data from
the patient and device links, then presents it to the patient and
healthcare providers in an extremely quick and easy to understand
format. The largest group that will benefit from PMAR are those
patients taking multiple chronically administered medications that
are essential to wellness. Another important population are
patients who are receiving medications that create frequent or
severe adverse drug reactions (ADRs). Typical examples of
healthcare providers are all physicians, pharmacists, nurse
practitioners, physician assistants, clinical trial personnel, and
any other health related professions who advise, monitor or treat,
patients with medications.
[0153] When patients visit their physician or other health care
providers, they are usually asked to produce a comprehensive,
up-to-date, and accurate list of all their medications including
the name of the drug, the dosage strength, and the directions for
use. This list can become extremely complex very quickly and
difficult to recall. This list is immensely valuable when a patient
is traveling and in an accident. It may be life saving if this
medication list can be produced as quickly as possible with all the
required details. Having an electronic copy immediately available
can save the patient time and money while improving their health
and possibly preventing an inappropriate drug related catastrophe.
A common example is when one of over 20 million Americans with
diabetes becomes extremely weak in a public place. If he/she has
recently taken his blood sugar lowering agent, a liquid with
concentrated sugar e.g. a soft drink or orange drink may save their
life. The patient must provide their username and password to allow
others access to this encrypted information. Since this protected
information resides on their cell phone, access to cellular service
is not required. A back-up of all this protected information can
also be accessed by the patient and any healthcare provider, family
member or close friend who has access.
[0154] If the patient has access to the Internet via their cell
phone or personal computer, they will be able to click a drug from
their drug list and be linked to drug-specific information in
Wikipedia. They will be reminded to print the information and have
it validated for its accuracy and personalized application to their
situation based upon various factors that are relevant, e.g., all
their existing disease stated, medication list, age, sex, weight,
diet, and exercise program.
Medication and Refill Reminders
[0155] The Reminder feature of PMAR provides a timely visual and
auditory notice to the patient via their mobile phone allowing the
customer to be alerted for each of their scheduled medications.
PMAR is easily customizable as to each patients preference as to
how they are to be reminded and the sound/vibrate/visual
notification rules governing the reminder system. They can reminded
to take all their prescription medications (Rx's), OTCs, herbal
medications, and nutritional supplements. This information is
stored in their cell phone calendar and also does not require
access to a cellular network.
[0156] PMAR will also remind the patient several days prior to
completing their medication that it is time to obtain a new refill
or if they are probably almost out of their OTC, herbal, and
nutrition supplement. This prevents one of the leading causes of
proper medication adherence. These reminders are based upon the
date of the last refill and whether they received a weekly,
monthly, or quarterly refill.
[0157] Although reminder systems are not uncommon, when coupled to
compliance monitoring systems, additional features become possible.
For example, if medications are not ingested when requested, a
series of reminders or alerts can be sent starting with the patient
and following up with family, care givers, doctors, pharmacists,
drug trial monitors and administrators. If necessary, the system or
support personnel can call or visit the patient to ensure that
there are no problems and that the patient is taking the medication
regularly.
Adverse Drug Reaction Report (ADR)
[0158] When the patient is reminded to take their medication, one
of their options will be to choose from a list of common side
effects and ADRs to document if they have experienced a recent ADR
and if they stopped taking their medication secondary to the ADR.
This often happens without the pharmacist or physician being aware.
This will assist healthcare providers in determining the cause of
patient non-adherence and prompt them to possibly decrease the dose
or select an alternative medication. This feature alone can help
decrease many avoidable hospitalizations.
Other Features
[0159] Referring again to FIG. 1, as an alternate to detection of
the pill in the gastrointestinal system, it is also possible to
detect a pill 30 as it passes through the esophagus E using a
sensor 32 designed to fit around the neck 33. Preferably, this
sensor 32 takes the form of a complete circle around the neck 33, a
partial, horseshoe-like enclosure, or a simple device held against
the neck 33. The sensor 32 detects all embodiments of the pill 30
described elsewhere as it passes through the esophagus E into the
stomach S. The embodiments in which the sensor 32 forms a semi- or
full circle around the neck 33 also improve the signal-to-noise
ratio over a sensor that is simply held in front of the patient.
There is also less dependence on digestive mechanisms, providing
less design restrictions on the pill itself.
[0160] The neck sensor operates in all the same ways as the
gastrointestinal reader ii, but also allows for other, possibly
advantageous, protocols. For the case in which multiple pills must
be detected, a protocol in which the patient takes one pill at a
time can be employed. In this approach, only one pill will occupy
the esophagus E at any time, which improves the sensor's capability
to identify and tally dosage.
[0161] The above specification and the drawings have been used to
disclose a number of embodiments of this invention. Specific terms
have been used in a descriptive sense only and not for purposes of
limitations. It will be appreciated by those skilled in the art
that various changes and modifications can be made in the above
described embodiments without departing from the spirit and scope
of this invention.
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