U.S. patent application number 15/131030 was filed with the patent office on 2016-08-11 for endovascular devices and methods of use.
The applicant listed for this patent is VASONOVA, INC.. Invention is credited to E. Tina Cheng, Sorin Grunwald, Bradley Hill.
Application Number | 20160228019 15/131030 |
Document ID | / |
Family ID | 39745526 |
Filed Date | 2016-08-11 |
United States Patent
Application |
20160228019 |
Kind Code |
A1 |
Grunwald; Sorin ; et
al. |
August 11, 2016 |
ENDOVASCULAR DEVICES AND METHODS OF USE
Abstract
An endovascular device includes an elongate body having a
proximal end and a distal end, an endovascular electrogram lead, a
balloon, a processor and a memory. The endovascular electrogram
lead and the balloon are on the distal end of the elongate body.
The balloon is expandable from a fully stowed configuration to an
expanded configuration. The processor receives and processes an
endovascular electrogram signal from the endovascular electrogram
lead. The memory stores instructions which, when executed by the
processor, cause the processor to: determine one or more
electrogram features based on the endovascular electrogram signal;
determine a position of the elongate body within the vasculature of
the patient based on the one or more electrogram features; and
initiate expansion of the balloon to the expanded configuration
based on the determined position of the elongate body within the
vasculature of the patient.
Inventors: |
Grunwald; Sorin; (Palo Alto,
CA) ; Hill; Bradley; (Santa Clara, CA) ;
Cheng; E. Tina; (Union City, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
VASONOVA, INC. |
Sunnyvale |
CA |
US |
|
|
Family ID: |
39745526 |
Appl. No.: |
15/131030 |
Filed: |
April 18, 2016 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
12359195 |
Jan 23, 2009 |
9339207 |
|
|
15131030 |
|
|
|
|
12147401 |
Jun 26, 2008 |
8597193 |
|
|
12359195 |
|
|
|
|
11431140 |
May 8, 2006 |
9204819 |
|
|
12147401 |
|
|
|
|
11431118 |
May 8, 2006 |
9198600 |
|
|
12147401 |
|
|
|
|
11431093 |
May 8, 2006 |
|
|
|
12147401 |
|
|
|
|
11430511 |
May 8, 2006 |
8409103 |
|
|
12147401 |
|
|
|
|
60937280 |
Jun 26, 2007 |
|
|
|
60957316 |
Aug 22, 2007 |
|
|
|
61023183 |
Jan 24, 2008 |
|
|
|
60678209 |
May 6, 2005 |
|
|
|
60682002 |
May 18, 2005 |
|
|
|
60678209 |
May 6, 2005 |
|
|
|
60682002 |
May 18, 2005 |
|
|
|
60678209 |
May 6, 2005 |
|
|
|
60682002 |
May 18, 2005 |
|
|
|
60678209 |
May 6, 2005 |
|
|
|
60682002 |
May 18, 2005 |
|
|
|
61023183 |
Jan 24, 2008 |
|
|
|
61023176 |
Jan 24, 2008 |
|
|
|
61023179 |
Jan 24, 2008 |
|
|
|
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 2017/00044
20130101; A61B 8/06 20130101; G09B 23/288 20130101; A61B 5/026
20130101; A61B 8/488 20130101; A61B 2034/2051 20160201; A61B 7/04
20130101; A61B 8/12 20130101; A61B 8/445 20130101; A61B 2090/064
20160201; A61B 5/042 20130101; A61B 2034/2055 20160201; A61B 8/0841
20130101; A61B 8/463 20130101; A61B 5/065 20130101; A61B 5/7405
20130101; A61B 8/42 20130101; A61B 8/465 20130101; A61B 5/0472
20130101; A61B 5/061 20130101; A61B 5/742 20130101; A61B 2034/252
20160201; A61B 8/565 20130101; A61B 5/0488 20130101; A61B 2090/062
20160201; A61B 8/08 20130101; A61B 5/1459 20130101; A61B 5/6853
20130101; A61B 8/461 20130101; A61B 5/029 20130101; A61B 2017/00106
20130101; A61B 34/20 20160201; A61B 5/0205 20130101; A61B 34/25
20160201; A61B 2017/00115 20130101; A61B 2017/22067 20130101; A61B
2090/378 20160201; A61B 5/06 20130101; A61B 5/0452 20130101; A61B
8/02 20130101; A61B 5/0456 20130101; A61B 5/0476 20130101; A61B
5/0215 20130101 |
International
Class: |
A61B 5/042 20060101
A61B005/042; A61B 8/08 20060101 A61B008/08; A61B 8/12 20060101
A61B008/12; A61B 8/02 20060101 A61B008/02; A61B 5/00 20060101
A61B005/00; A61B 5/0452 20060101 A61B005/0452 |
Claims
1. An endovascular device, comprising: an elongate body having a
proximal end and a distal end; an endovascular electrogram lead on
the distal end of the elongate body in a position such that, when
the endovascular device is in a vessel of the vasculature of a
patient, the endovascular electrogram lead is in contact with
blood; a balloon on the distal end of the elongate body adjacent to
the endovascular electrogram lead, the balloon being configured to
expand from a fully stowed configuration to an expanded
configuration; a processor configured to receive and process an
endovascular electrogram signal from the endovascular electrogram
lead; and a memory configured to store instructions which, when
executed by the processor, cause the processor to: determine one or
more electrogram features based on the endovascular electrogram
signal; determine a position of the elongate body within the
vasculature of the patient based on the one or more electrogram
features; and initiate expansion, based on the determined position
of the elongate body within the vasculature of the patient, of the
balloon to the expanded configuration.
2. The endovascular device of claim 1, wherein: the processor is
further configured to receive and process a second endovascular
electrogram signal from the endovascular electrogram lead after the
balloon is in the expanded configuration; and the memory is further
configured to store instructions which, when executed by the
processor, cause the processor to: determine one or more second
electrogram features based on the endovascular electrogram signal;
and determine cardiac function based on the one or more second
electrogram features.
3. The endovascular device of claim 1, wherein the memory is
further configured to store instructions which, when executed by
the processor, cause the processor to initiate stopping of the
expansion of the balloon after the expansion of the balloon has
been initiated.
4. The endovascular device of claim 1, wherein the memory is
further configured to store instructions which, when executed by
the processor, cause the processor to initiate deflation of the
balloon after the expansion of the balloon has been stopped.
5. The endovascular device of claim 1, wherein the memory is
further configured to store instructions which, when executed by
the processor, cause the processor to initiate partial expansion of
the balloon, such that blood flow within the vasculature of the
patient carries the elongate body by pushing the partially expanded
balloon.
6. The endovascular device of claim 1, wherein the position of the
elongate body within the vasculature of the patient is a pulmonary
artery, a branch of the pulmonary artery, or a pulmonary artery
wedge position.
7. The endovascular device of claim 1, wherein the balloon is
proximal to the endovascular electrogram lead on the distal end of
the elongate body.
8. The endovascular device of claim 1, wherein the one or more
electrogram features include characteristics of the P-wave, the QRS
complex, or the T-wave of one or more electrocardiograms of the
endovascular electrogram signal.
9. The endovascular device of claim 8, wherein the one or more
electrogram features include a P-wave amplitude of the one or more
electrocardiograms of the endovascular electrogram signal.
10. The endovascular device of claim 1, wherein the elongate body
is a catheter.
11. The endovascular device of claim 1, further comprising a
non-imaging ultrasound transducer on the distal end of the elongate
body, the non-imaging ultrasound transducer being configured to
transmit a first non-imaging ultrasound signal into the vessel of
the vasculature of the patient and to receive a first reflected
non-imaging ultrasound signal.
12. The endovascular device of claim 11, wherein the non-imaging
ultrasound transducer is distal to the endovascular electrogram
lead on the distal end of the elongate body.
13. The endovascular device of claim 11, wherein: the processor is
further configured to receive and process a signal from the
non-imaging ultrasound transducer; and the memory is further
configured to store instructions which, when executed by the
processor, cause the processor to determine the position of the
elongate body within the vasculature of the patient based on the
one or more electrogram features and the signal from the
non-imaging ultrasound transducer.
14. The endovascular device of claim 13, wherein the processor is
further configured to determine a first blood flow signature
pattern based on the first reflected non-imaging ultrasound signal,
the first blood flow signature pattern being different from the
first reflected non-imaging ultrasound signal.
15. The endovascular device of claim 14, wherein the first blood
flow signature pattern includes first blood flow velocities or
first pressure signature patterns.
16. The endovascular device of claim 15, wherein the first blood
flow velocities include a first blood flow velocity towards the
non-imaging ultrasound transducer and a first blood flow velocity
away from the non-imaging ultrasound transducer.
17. The endovascular device of claim 16, wherein the first blood
flow signature pattern includes a ratio of the first blood flow
velocity towards the non-imaging ultrasound transducer and the
first blood flow velocity away from the non-imaging ultrasound
transducer.
18. The endovascular device of claim 15, wherein the first pressure
signature patterns include a first blood flow power spectrum
towards the non-imaging ultrasound transducer and a first blood
flow power spectrum away from the non-imaging ultrasound
transducer.
19. The endovascular device of claim 13, wherein: the processor is
further configured to receive and process a second signal from the
non-imaging ultrasound transducer after the balloon has initiated
expansion; and the memory is further configured to store
instructions which, when executed by the processor, cause the
processor to: determine that blood flow through the vessel of the
vasculature of the patient has stopped based on the second signal
from the non-imaging ultrasound transducer; and initiate stopping
of the expansion of the balloon while maintaining the stoppage of
flow through the vessel in response to the determination that blood
flow through the vessel of the vasculature of the patient has
stopped.
20. The endovascular device of claim 11, wherein the first
non-imaging ultrasound signal is an A-mode ultrasound signal or a
Doppler ultrasound signal.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a Continuation of U.S. patent
application Ser. No. 12/359,159, filed Jan. 23, 2009, and published
as U.S. Patent App. Pub. No. 2009/0177090 on Jul. 9, 2009, which
claims the benefit of U.S. Provisional Patent App. No. 61/023,183,
filed Jan. 24, 2008, U.S. Provisional Patent App No. 61/023,176,
filed Jan. 24, 2008, and U.S. Provisional Patent App. No.
61/023,179, filed Jan. 24, 2008, each of which is incorporated
herein by reference in its entirety.
[0002] This application is also a Continuation-in-Part of U.S.
patent application Ser. No. 12/147,401, filed Jun. 26, 2008, and
issued as U.S. Pat. No. 8,597,193 on Dec. 3, 2013, which claims the
benefit of U.S. Provisional Patent App. No. 60/937,280, filed Jun.
26, 2007, U.S. Provisional Patent App. No. 60/957,316, filed Aug.
22, 2007, and U.S. Provisional Patent App. No. 61/023,183, filed
Jan. 24, 2008, each of which is incorporated herein by reference in
its entirety.
[0003] U.S. patent application Ser. No. 12/147,401 is a
Continuation-in-Part of U.S. patent application Ser. No.
11/431,140, filed May 8, 2006, and issued as U.S. Pat. No.
9,204,819 on Dec. 8, 2015; U.S. patent application Ser. No.
11/431,118, filed May 8, 2006, and issued as U.S. Pat. No.
9,198,600 on Dec. 1, 2015; U.S. patent application Ser. No.
11/431,093, filed May 8, 2006, and published as U.S. Patent App.
Pub. No. 2007/0016069 on Jan. 18, 2007; and U.S. patent application
Ser. No. 11/430,511, filed May 8, 2006, issued as U.S. Pat. No.
8,409,103, on Apr. 2, 2013, all of which claim the benefit of U.S.
Provisional Patent App. No. 60/678,209, filed May 6, 2005, and U.S.
Provisional Patent App. No. 60/682,002, filed May 18, 2005, each of
which is incorporated herein by reference in its entirety.
BACKGROUND OF THE INVENTION
[0004] The invention relates to the guidance, positioning and
placement confirmation of intravascular devices, such as catheters,
stylets, guidewires and other elongate bodies that are typically
inserted percutaneously into the venous or arterial vasculature,
including flexible elongate bodies. Currently these goals are
achieved using x-ray imaging and in some cases ultrasound imaging.
This invention provides a method to substantially increase the
accuracy and reduce the need for imaging related to placing an
intravascular catheter or other device. Reduced imaging needs also
reduce the amount of radiation that patients are subjected to,
reduce the time required for the procedure, and decrease the cost
of the procedure by reducing the time needed in the radiology
department.
[0005] The vasculature of mammals has long been accessed to provide
therapy, administer pharmacological agents and meet other clinical
needs. Numerous procedures exist in both venous and arterial
systems and are selected based on patient need. One challenge
common to all vascular-based therapies is health care provider
access to the specific location or section of the vascular
tree.
[0006] One common venous access procedure is central venous access.
Central venous access is the placement of a venous catheter in a
vein that leads directly to the heart. Central venous catheters are
ubiquitous in modern hospital and ambulatory medicine, with up to 8
million insertions per year in the U.S. and a similar number
outside the U.S.
[0007] Venous access devices are most often used for the following
purposes: [0008] Administration of medications, such as
antibiotics, chemotherapy drugs, and other IV drugs [0009]
Administration of fluids and nutritional compounds
(hyperalimentation) [0010] Transfusion of blood products [0011]
Hemodialysis [0012] Multiple blood draws for diagnostic
testing.
[0013] Central venous access devices are small, flexible tubes
placed in large veins for people who require frequent access to
their bloodstream. The devices typically remain in place for long
periods: week, months, or even longer.
[0014] Central venous access devices are usually inserted in 1 of 3
ways: [0015] a) Directly via a catheter. Catheters are inserted by
tunneling under the skin into either the subclavian vein (located
beneath the collarbone) or into the internal jugular vein (located
in the neck). The part of the catheter where medications are
administered or blood drawn remains outside of the skin. [0016] b)
Through a port. Unlike catheters, which exit from the skin, ports
are placed completely below the skin. With a port, a raised disk
about the size of a quarter or half dollar is felt underneath the
skin. Blood is drawn or medication delivered by placing a tiny
needle through the overlying skin into the port or reservoir.
[0017] c) Indirectly via a peripheral vein. Peripherally inserted
central catheter (PICC) lines, unlike central catheters and ports,
are not inserted directly into the central vein. A PICC line is
inserted into a large vein in the arm and advanced forward into the
larger subclavian vein.
[0018] Central catheters and ports are usually inserted by a
surgeon or surgical assistant in a surgical suite. An alternative
is placement under the guidance of a special x-ray machine so that
the person inserting the line can make sure that the line is placed
properly. A PICC line can be put in at bedside, usually by a
specially trained nurse. In this later case, confirmation by X-ray
is currently required for assessing the success of the PICC
placement.
[0019] Traditional surgically placed central catheters are
increasingly being replaced by peripherally inserted central venous
access devices. PICC lines usually cause fewer severe complications
than central venous access devices.
Peripherally-Inserted-Central-Catheter (PICC) is used in a variety
of clinical procedures. The PICC line placement procedure is
performed by interventional radiologists to deliver long-term drug
delivery, chemotherapy procedures, delivery of intravenous
medications or intravenous nutrition (hyperalimentation) and taking
blood samples via a Hickman catheter. Insertion of PICC lines is a
routine procedure in that it is carried out fairly often for a
variety of treatments, and more than once in the same patient when
the catheter is to be left in place for any length of time. Even
though it is routine, it is a very time and labor-intensive
procedure for the hospital staff, which also makes it expensive.
During the procedure the physician or nurse places the catheter
into a superficial arm vein such as the cephalic, basilic,
antecubital, median cubital, or other superficial vein with the
goal of having the distal end of the catheter reach the superior
vena cava. After entering the superficial vein around the area
where the arm bends (elbow), the catheter is advanced up the
subclavian vein, then the brachiocephalic vein and finally it
enters the superior vena cava. One caveat is to make sure that the
PICC line does not enter the jugular vein via the subclavian
vein.
[0020] Pulmonary artery catheterization is another example of a
procedure utilizing venous access procedures. Pulmonary Artery
Catheters (PAC), also knows as Swan-Ganz or right heart catheters,
provide information regarding the central venous, right heart, and
pulmonary arterial blood pressures, thermodilution measurements
that are useful for calculating cardiac output and related
physiological parameters, access for drug delivery, and blood
sampling at various intervals along the length of the catheter.
PACs can lead to several complications in a patient. These
complications include arrhythmias, rupture of the pulmonary artery,
thrombosis, infection, pneumothorax, bleeding, etc. Complications
can arise due to improper insertion, use, and/or maintenance of the
catheter in the patient.
[0021] Hemodialysis therapy via a hemodialysis catheter is another
example of a procedure requiring central venous access. A dialysis
catheter is a specialized type of central venous catheter used for
dialysis. Dialysis catheter placement involves the insertion of a
catheter into a large vessel, utilizing X-ray guidance. The
challenges of inserting a hemodialysis catheter in terms of
guidance and positioning are similar to those of a central venous
catheter, only they are typically larger and require a peel-away
sheath for insertion.
[0022] Another therapy achieved via providing access to the venous
system is the percutaneous treatment of varicose veins. Published
population studies indicate that approximately 25 million people in
the U.S. and 40 million people in Western Europe suffer from
symptomatic venous reflux disease. Percutaneous treatment of
varicose veins involves the placement of an energy delivery
catheter (laser or RF) after navigation the vasculature to locate
the treatment site. One common treatment site is the
sapheno-femoral junction and less common sites are the
sapheno-popliteal junction and sites of perforator veins, which
connect the superficial venous system to the deep venous system of
the leg at a variety of different locations, mostly below the knee.
As such, in the case of percutaneous treatment of varicose veins
using specific venous junctions, the position the laser or the RF
catheter at an optimal location with respect to the venous junction
is critical for the success of the intervention.
[0023] In addition to guiding the catheter through the vasculature,
the location of the catheter tip is very important to the success
of the procedure. Catheters will generally function equally well
for pressure measurement and fluid infusion if the tip is situated
in any major vein, above or below the heart. For dialysis or the
infusion of irritant/hypertonic fluids, a high rate of blood flow
past the catheter tip is desirable and this requires the placement
of the luminal opening in as large a vessel as possible. However,
the package inserts of many central venous catheters give very
strong warnings about the absolute requirement for catheter tips to
lie outside the heart to avoid perforation and subsequent
pericardial tamponade. Likewise positioning the catheter tip away
from small peripheral veins is important to avoid damaging the vein
wall or occluding the vein due the caustic effects of the infusing
solution. It is also of major interest that the catheter tip stays
in place after placement for the whole duration of the treatment.
If the catheter tip moves, not only its effectiveness diminished
but, in some situations, it can perforate the heart. In the United
States, the Food and Drug Administration has issued advice
emphasizing this point. Typically, the interventional radiologist
uses a fluoroscopic agent to delineate the veins in the body and
subsequently verifies the correct positioning of the catheter tip
using a post-operative X-ray. Currently, post-operative X-ray is
performed routinely while some studies have shown that only 1.5% of
the cases are subject to complications that would indeed require
X-ray imaging.
[0024] Current methods for guiding PICC lines include external
electromagnetic sensors and intravascular, e.g., ECG. N the case of
electromagnetic sensors, the endovascular device is guided by
assessing the distance between an electromagnetic element at the
tip of the device, e.g., a coil and an external (out of body)
receiver. This method is inaccurate because it does not actually
indicate location in the vascular but distance to an outside
reference. In the case of ECG-guided catheters, the classic
increase in P-wave size, known as "P-atriale", is a widely accepted
criterion for determining location of central venous catheter tips
in the proximity of the sino-atrial node. Current methods include
using a catheter filled with saline and an ECG adaptor at the
proximal end connected to an ECG system. This method is inaccurate
because it does not indicate location in the blood vessel but the
proximity of the sino-atrial node. Because of known inaccuracies,
all the current methods in use do explicitly require the use of a
confirmatory chest X-ray to verify and confirm location of the tip
of the endovascular device at the desired target in the
vasculature. Most prior art relating to the use of intravascular
ultrasound or electrical mapping of heart activity for diagnostic
and therapeutic purposes addresses problems independently: some
addresses ultrasound guidance on the arterial side such as that
described by Franzin in Doppler-guided retrograde catheterization
using transducer equipped guide wire (U.S. Pat. No. 5,220,924) or
that described by Katims in Method and apparatus for locating a
catheter adjacent to a pacemaker node of the heart (U.S. Pat. No.
5,078,678). Such approaches have intrinsic limitations which does
not make them suited to solve the problem addressed by the current
invention. The limitations of the Franzin approach have been
extensively explained in VasoNova patent applications US
20070016068, 20070016069, 20070016070, and 20070016072. Limitations
of an approach based exclusively on measuring right-atrial
electrocardiograms have been described in the literature, for
example in [1]: W. Schummer et al., Central venous catheters--the
inability of `intra-atrial ECCG` to prove adequate positioning,
British Journal of Anaesthesia, 93 (2): 193-8, 2004.
[0025] What is needed are methods and apparatuses to optimize
guidance and placement of catheters in order to reduce the risk
associated with wrong placement and the cost associated with the
X-ray imaging. Further there remains a need for a catheter guidance
and placement system that may be used to safely guide and place
catheters in healthcare provider or clinical environments other
than in the radiology department or surgical suite wherein a
radiological or other external imaging modality is used to confirm
catheter placement. As such, there remains a need in the medical
arts for instruments, systems and associated methods for locating,
guiding and placing catheters and other instruments into the
vasculature generally. In addition remains a need in the medical
arts for instruments, systems and associated methods for locating,
guiding and placing catheters and other instruments into the
vasculature to meet the challenges presented by the unique
characteristics and attributes specific to the vascular system of
interest. The current invention overcomes the above described
limitations by making use of physiological parameters like blood
flow and ECG measured in the vasculature and is based on the fact
that physiological parameters and their relationship is unique to
the locations in the vasculature where the endovascular devices
needs to be placed. The current invention describes an apparatus
for identifying the unique physiological signature of a certain
location in the vasculature and a method to guide the endovascular
device to that location based on the physiological signatures.
SUMMARY OF THE INVENTION
[0026] An aspect of the invention includes a method of evaluating
flow characteristics in a vessel of a patient. In some embodiments,
the method includes the steps of positioning a catheter having a
balloon at a measuring location within the vessel; transmitting an
ultrasound signal into the vessel while the balloon catheter is
within the measuring location; evaluating a reflection of the
ultrasound signal to determine a flow parameter within the vessel
while the catheter is in the measuring position; expanding the
balloon within the vessel at the measuring location; and stopping
the expanding step when the result of the evaluating step is that
the flow through the vessel is substantially stopped. In some
embodiments, the measuring location is within a pulmonary artery,
within a branch of the pulmonary artery, and/or is a pulmonary
artery wedge position.
[0027] In some embodiments, the transmitting step further comprises
transmitting an ultrasound signal into the vessel from an
ultrasound transducer on the balloon catheter. In some embodiments,
the transmitting step further comprises transmitting an ultrasound
signal into the vessel during the expanding step. In some
embodiments, the transmitting step further comprises transmitting a
non-imaging ultrasound signal into the vessel. In some embodiments,
the transmitting step further comprises transmitting an A-mode
ultrasound signal into the vessel. While in some embodiments, the
transmitting step further comprises transmitting Doppler ultrasound
signal into the vessel.
[0028] In some embodiments, the evaluating step further comprises
receiving a reflected ultrasound signal with an ultrasound
transducer on the balloon catheter. In some embodiments, the
evaluating step further comprises determining blood flow velocity
and/or blood flow intensity within the vessel and the stopping step
further comprises stopping the expanding step when the determined
blood flow velocity and/or blood flow intensity indicates that the
flow through the vessel has substantially stopped. In some
embodiments, the evaluating step further comprises determining a
blood flow signature pattern within the vessel and the stopping
step further comprises stopping the expanding step when the
determined blood flow signature pattern indicates that the flow
through the vessel has substantially stopped. In some embodiments,
the evaluating step further comprises determining a pressure
signature pattern within the vessel and the stopping step further
comprises stopping the expanding step when the determined pressure
signature pattern indicates that the flow through the vessel has
substantially stopped. In some embodiments, the stopping step
further comprises stopping the expansion of the balloon when the
ultrasound transducer receives a reflected ultrasound signal that
indicates that the flow through the vessel has substantially
stopped. In some embodiments, the stopping step further comprises
stopping the expanding step when the result of the evaluating step
is that the pressure at the measuring location within the vessel
has dropped below the mean pulmonary arterial pressure. In some
embodiments, the stopping step further comprises stopping the
expanding step when the result of the evaluating step is that the
pressure signature pattern at the measuring location within the
vessel is consistent with a pulmonary capillary wedge pressure
signature pattern. In some embodiments, the pressure signature
pattern indicates a pressure lower than a pulmonary artery pressure
and a pressure more static than a pulmonary artery pressure. In
some embodiments, the stopping further comprises stopping the
expanding step when the balloon expanding pressure is at least
equal to a systolic pulmonary arterial pressure.
[0029] In some embodiments, the method further comprises the step
of deflating the balloon. In some embodiments, the evaluating step
further comprises evaluating a reflection of the ultrasound signal
to determine a flow parameter within the vessel after the balloon
is deflated. In some embodiments, the evaluating step further
comprises determining a blood flow signature pattern within the
vessel. In some embodiments, wherein the blood flow signature
pattern indicates turbulent blood flow as the balloon deflates and
decouples from the vessel wall. In some embodiments, the method
further comprises the step of verifying that flow parameter within
the vessel determined after the balloon is deflated is
substantially similar to the flow parameter within the vessel
determined before the balloon is inflated.
[0030] In some embodiments, the method further comprises the step
of detecting an endovascular electrogram signal with a sensor on
the endovascular device. In some embodiments, the endovascular
electrogram comprises electrical activity from the heart, while in
some embodiments the electrical activity of the heart is related to
the sino-atrial node of the heart. In some embodiments, the timing
of the expanding step is based on the electrogram signal. In some
embodiments, the result of the evaluating step is a combined
evaluation of the ultrasound signal and the electrogram signal. In
some embodiments, the method further comprises the step of
measuring a parameter used to determine cardiac function. In some
embodiments, the measuring step further comprises measuring
pulmonary artery occlusion pressure. In some embodiments, the
timing of the measuring step is based on the electrogram signal,
and in some embodiments, the measuring step further comprises
measuring arterial flow.
[0031] In some embodiments, the positioned step further comprises
the steps of advancing the balloon catheter into the vessel;
transmitting an ultrasound signal into the vessel using an
ultrasound transducer on the balloon catheter; receiving a
reflected ultrasound signal with the ultrasound transducer; and
positioning the endovascular device based on the ultrasound signal.
In some embodiments, the method further comprises the step of
processing the reflected ultrasound signal received by the
ultrasound transducer. In some embodiments, the result of the
processing step includes information related to blood flow
direction. In some embodiments, the flow direction comprises a flow
directed towards the sensor and a flow directed away from the
sensor. In some embodiments, the result of the processing step
includes information related to blood flow velocity and/or blood
flow intensity. In some embodiments, the result of the processing
step includes information related to ultrasound A-mode
information.
[0032] Another aspect of the invention includes a method of
evaluating flow characteristics in a vessel of a patient. In some
embodiments, the method includes the steps of positioning a
catheter having a balloon at a measuring location within the
vessel; transmitting a first ultrasound signal into the vessel
while the balloon catheter is within the measuring location;
evaluating a reflection of the first ultrasound signal to determine
a first flow parameter of the vessel while the balloon is in a
first configuration; expanding the balloon within the vessel at the
measuring location; transmitting a second ultrasound signal into
the vessel during the expanding step; evaluating a reflection of
the second ultrasound signal to determine when the blood flow
through the vessel is substantially stopped; returning the balloon
to the first configuration; transmitting a third ultrasound signal
into the vessel after the returning step; and evaluating a
reflection of the third ultrasound signal to determine a third
blood flow parameter of the vessel. In some embodiments, the first
configuration of the balloon is a stowed configuration, while in
some embodiments the first configuration of the balloon is a
partially inflated configuration. In some embodiments, the method
further comprises the step of verifying that first flow parameter
of the vessel is substantially similar to the third flow parameter
of the vessel.
[0033] Another aspect of the invention includes a method of
evaluating flow characteristics in a vessel of a patient. In some
embodiments, the method includes the steps of positioning a
catheter having a balloon at a measuring location within the
vessel; transmitting an ultrasound signal into the vessel while the
balloon catheter is within the measuring location; detecting an
electrogram signal while the balloon catheter is within the
measuring location; evaluating a reflection of the ultrasound
signal and the electrogram signal while the catheter is in the
measuring position; expanding the balloon within the vessel at the
measuring location; stopping the expanding step when the result of
the evaluating step is that the flow through the vessel is
substantially stopped; and measuring a parameter used to determine
cardiac function, wherein the timing of the measuring step is based
on the result of the evaluation step. In some embodiments, the
result of the evaluating step is a combined evaluation of the
ultrasound signal and the electrogram signal.
[0034] Another aspect of the invention includes a balloon catheter
system. In some embodiments, the balloon catheter system includes a
catheter adapted and configured to be inserted into a patient's
vasculature, an expandable balloon coupled to the catheter towards
the distal end of the catheter, and an ultrasound sensor coupled to
the catheter distal to the balloon. In some embodiments, the
balloon catheter is a Swan-Ganz catheter. In some embodiments, the
catheter may be at least 55 to 75 cm in length, and may include
incremental markings to gauge insertion length. In some
embodiments, the catheter includes multiple lumens. In some
embodiments, the balloon is expandable. In some embodiments, the
balloon has a first configuration. In some embodiments, the first
configuration may be a fully stowed configuration, or in some
embodiments, the first configuration is a partially inflated
position. In some embodiments, the balloon catheter system may
further include an ECG sensor coupled to the catheter distal to the
balloon. In some embodiments, the balloon catheter may include more
than one ECG sensor. In some embodiments, the ECG sensors are
spaced along the catheter at various intervals.
INCORPORATION BY REFERENCE
[0035] All patents, publications and patent applications mentioned
in this specification are herein incorporated by reference in their
entirety to the same extent as if each individual patent,
publication or patent application was specifically and individually
indicated to be incorporated by reference.
BRIEF DESCRIPTION OF THE DRAWINGS
[0036] The novel features of the invention are set forth with
particularity in the appended claims. A better understanding of the
features and advantages of the present invention will be obtained
by reference to the following detailed description that sets forth
illustrative embodiments, in which the principles of the invention
are utilized, and the accompanying drawings of which:
[0037] FIG. 1 illustrates an overview of the endovascular device
guiding apparatus and method disclosed in the present
invention.
[0038] FIG. 2 illustrates an endovascular device with multiple
sensors.
[0039] FIG. 3A-3B illustrates an intravascular ECG electrode which
can be used for steering and moving the endovascular member away
from the vessel wall.
[0040] FIG. 4A-4C illustrates the concept of removable sensor core,
whereby a stylet with integrated sensors can be inserted into and
removed from an endovascular device like a catheter at any
time.
[0041] FIG. 5A-5B illustrates an embodiment integrated sensors in
an endovascular device with braided shaft and atraumatic tip.
[0042] FIG. 6 illustrates another embodiment of integrated sensors
in an endovascular device with stylet-like reinforcement that can
be used as an ECG electrode.
[0043] FIG. 7 illustrates the flow velocity profiles, the
intravascular ECG signal and their correlation as detected by the
device according to the present invention in the superior vena cava
as documented by the synchronized fluoroscopic image.
[0044] FIG. 8 illustrates the flow velocity profiles, the
intravascular ECG signal and their correlation as detected by the
device according to the present invention at the caval-atrial
junction as documented by the synchronized fluoroscopic image.
[0045] FIG. 9 illustrates the flow velocity profiles, the
intravascular ECG signal and their correlation as detected by the
device according to the present invention in the internal jugular
vein as documented by the synchronized fluoroscopic image.
[0046] FIG. 10 illustrates the use of intravascular ECG signal to
gate or trigger the acquisition or processing of the blood flow
information.
[0047] FIG. 11 illustrates the effect of using additional gating
based on patient's breathing on the acquisition and processing of
blood flow information.
[0048] FIG. 12 illustrates the use of intravascular ECG signals in
case of a-fib patients.
[0049] FIG. 13 illustrates a graphical user interface displaying
blood flow information, intravascular ECG signals, their
correlation, and catheter tip location information based on the
above. FIG. 13 also illustrates the use of A-mode imaging for clot
identification inside the blood stream or inside an endovascular
member.
[0050] FIG. 14A-14D illustrates a simplified user interface using
blood flow information, intravascular ECG signals and their
correlation to display if the endovascular member is advancing
towards the caval-atrial junction and sinoatrial node, if the
endovascular member is advancing away from the caval-atrial
junction and sinoatrial node, or if the endovascular member is at
the caval-atrial junction proximal to sinoatrial node.
[0051] FIG. 15 is a flow chart of an exemplary endovascular
placement method.
[0052] FIG. 16 illustrates an endovascular device within the
vasculature at various locations according to the method of FIG.
15.
[0053] FIGS. 17 and 18 are various views of the heart and
surrounding vasculature.
[0054] FIG. 19 is a flow chart illustrating the functioning of a
data acquisition system of FIG. 6.
[0055] FIG. 20 is a flow chart illustrating an exemplary software
block diagram of FIG. 6.
[0056] FIG. 21 is a flow chart illustrating an exemplary processing
algorithm for multi-parameter signal processing and
correlation.
[0057] FIGS. 22A and 22B illustrate an embodiment of a balloon
catheter including an ultrasound sensor and an ECG sensor.
[0058] FIGS. 23-27 are flow charts illustrating methods for
evaluating flow characteristics in a vessel.
DETAILED DESCRIPTION OF THE INVENTION
[0059] Embodiments of the present invention provide guided vascular
access devices, systems for processing signals from the guided
vascular access devices and user interface for providing
information to a user based on outputs from the processing system.
FIG. 1 illustrates one embodiment of an exemplary endovascular
access and guidance system 100. The system 100 includes an elongate
body 105 with a proximal end 110 and a distal end 115. The elongate
body 105 is any of a variety of endovascular devices adapted to
insertion into and navigation through the vasculature of the
patient 1. FIG. 1 illustrates the distal end 115 inserted into the
basilic vein 6. The expected path of travel (dashed line 20) in
this illustrative example is into the portion of the heart 20 or
within the superior vena cava 14 in proximity to the sinoatrial
node (SA node) 8. The aorta 3, the pulmonary arteries, pulmonary
veins 11, the jugular veins 10, the brachiocephalic vein 12,
inferior vena cava 16 and atrioventricular node (AV node) 9 are
also represented in this view.
[0060] Not shown in FIG. 1 but further described below, the
elongate body 105 includes at least two sensors for measuring
physiological parameters in the body. In some embodiments, one
sensor is a non-imaging ultrasound transducer on the elongate body
105 configured to provide in vivo non-image based ultrasound
information of the vasculature of the patient 1. In some
embodiments, the other sensor is an endovascular electrogram lead
on the elongate body 105 in a position that, when the elongate body
105 is in the vasculature, the endovascular electrogram lead
electrical sensing segment provides an in vivo electrogram signal
of the patient 1. FIG. 1 illustrates the use of a second
electrogram sensor that is outside of the vasculature. The
electrode 112 is positioned external to the vasculature of the
patient 1. The electrode 112 detects electrogram information that
is transmitted via lead 111 to the processor 140.
[0061] Alternatively, in place of the electrode 112 or in addition
to the electrode 112 another electrogram sensor may be placed on
the elongate body 105. More than one electrogram sensor may be
provided on the elongate body. In this case, the processor 140
would also be configured to receive, process, compare and correlate
the electrogram information from the additional electrogram sensor
(or other sensors) provided by the elongate body 105. The
electrogram leads or sensors on the elongate body 105 may also be
placed relative to the elongate body 105 and to one another in
order to obtain a target electrogram signal and a baseline
electrogram signal in order to facilitate the position and location
capabilities of the guidance system 100. The target and baseline
electrogram information may be related to one or more of: (a)
electrical activity of the heart including all or a portion of an
electrocardiogram (ECG); (b) electrical activity of the brain
including all or part of an electroencephalogram (EEG); and (c)
electrical activity of a muscle or muscle group including all or
part of an electromyogram (EMG) related to that muscle or muscle
group. Additional details of the sensors and the various
alternative configurations of the elongate body 105 are described
below in at least FIGS. 2-5B.
[0062] The system 100 also includes a processor 140 configured to
receive and process a signal from the non-imaging ultrasound
transducer and a signal from the endovascular electrogram lead. The
processor 140 includes conventional processing capabilities to
receive and process ultrasound and electrogram signals as with
conventional ultrasound and electrogram signals. The conventional
processing capabilities include those conventional components
needed to receive process and store the corresponding sensor data.
If sensors on the elongate body are used to detect ECG activity,
then appropriate electrocardiography components and processing
capabilities is provided. The same is true for EEG signal
processing, EMG signal processing, acoustic sensor processing,
pressure sensor processing, optical sensor processing and the
like.
[0063] However, unlike conventional ultrasound and electrogram
systems, processor 140 includes programming and processing
capabilities to process the signals from the sensors to identify
and correlate flow and electrical patterns to aid in the guidance,
positioning and confirmation of location of the elongate body 105
as described herein.
[0064] In one aspect, the processor 140 is adapted and configured
using software, firmware or other programming capabilities to
receive and process a signal from the non-imaging ultrasound
transducer that contains at least one signal of the group
consisting of: a venous blood flow direction, a venous blood flow
velocity, a venous blood flow signature pattern, a pressure
signature pattern, A-mode information and a preferential non-random
direction of flow. Additionally, the processor 140 is further
adapted and configured using software, firmware or other
programming capabilities to receive and process a signal from the
endovascular electrogram lead that contains at least one signal
from the group consisting of: an electrocardiogram signal, a P-wave
pattern, a QRS-complex pattern, a T-wave pattern, an EEG signal and
an EMG signal.
[0065] In one aspect, the signal from one sensor is the trigger for
acquisition or processing of a signal from another sensor. In this
manner, the data from two different physiologic sensors may be
correlated in time and to the trigger signal. Alternatively, rather
than triggering acquisition data from the triggered sensor, all
sensor data could be collected and/or stored and the trigger could
instead result in the processing of only the subset of the data
based on the trigger data. In either triggering scheme, the trigger
sensor data and the triggered sensor data are processed together to
yield the benefits described below. One example of triggering is
the use of the P-wave detection from an electrogram sensor as the
triggering signal for acquiring ultrasound data from an ultrasound
sensor. As described below, the unique P-wave signal detected when
an electrogram lead is positioned in the superior vena cava near
the sino-atrial node 8 can be used to confirm the detection of the
unique blood flow pattern that also occurs in this area of the
vasculature. In this way, the existence of both unique
physiological signals from two different physiological systems
increases the accuracy of the guidance system embodiments described
herein.
[0066] The system 100 also includes an output device 130 configured
to display a result of information processed by the processor 140.
The display device may, like the processor 140, include
capabilities found in conventional display devices. The display
device 140 of the invention differs from the conventional display
in that the display is configured to display information related to
the unique processing and results determined by processor 140. In
one aspect, the output device 140 displays a result related to a
position of the elongate body within the vasculature of the
patient. In another aspect, a result of information processed by
the processor includes an indication of a position or a movement of
the elongate body 105 within the vasculature based on in vivo
non-image based ultrasound information and in vivo electrogram
information. The display 130 would be configured to display this
information for a user to perceive in any suitable manner such as
visually, with colors, with pictograms, with sounds or in other
appropriate manners.
[0067] Other aspects of embodiments the invention relate to the use
of intravascularly measured physiological parameters for locating,
guiding, and placing catheters in the vasculature. In one aspect,
embodiments of the present invention relate to an endovascular
member assembly with built-in sensors for measuring of
physiological parameters such as blood flow, velocity, pressure, or
intravascular ECG. In a different aspect, embodiments of the
invention relate to data processing algorithms that can identify
and recognize different locations in the vasculature based on the
pattern of physiological parameters measured at that location. In
still another different aspect, embodiments of the present
invention relate to data processing algorithms that can identify
and recognize structures such as objects of interest in the
vasculature or in endovascular members, e.g., blood clots based on
the pattern of parameters measured, e.g., A-mode and blood flow
velocity. In an additional aspect, embodiments of the present
invention relate to an instrument that has a user interface which
shows guiding and positioning information and presents the objects
of interest, e.g., blood clots. For example, in this aspect the
processor is further configured to process a signal from the
non-image ultrasound transducer and to indicate in the output
device information related to the presence of a structure in the
field of view of the non-imaging ultrasound transducer.
[0068] In still another aspect, embodiments of the invention relate
to the method of guiding and positioning an endovascular member
within the vasculature by the user based on location information
provided by the sensor-based endovascular member. Other various
aspects of embodiments the invention relate to the use of
intravascularly measured physiological parameters for locating,
guiding, and placing catheters or stylets or guide wires for use as
guides to particular locations within the vasculature that have
been identified using the guided vascular access devices and
systems described herein.
[0069] The present invention provides a new methods, devices and
systems for intravascular guidance and placement of endovascular
devices based on the recognition of patterns in the signals for
different physiological parameters and correlation of those signal
patterns. In one exemplary application, a catheter, such as a
peripherally inserted central catheter (PICC) is inserted,
advanced, positioned and monitoring within the vasculature based on
the recognition of blood flow patterns, of the electrocardiogram
signals and of their correlation at the locations of interest.
[0070] One benefit of the new apparatus and method introduced
herein is that it increases the probability of correct placement of
an endovascular device in a placement procedure performed at the
bedside. Moreover, because of the accuracy and redundancy of the
positioning methods described herein, it is believed that the use
of the inventive methods, devices and systems will allow for
endovascular device placement without the need for imaging
guidance, in particular without X-ray imaging and/or imaging for
confirmation of placement and lack of device migration. Another
benefit of the new apparatus and method introduced herein is that
it allows the detection of blood clots in the vasculature or in
catheters such identifying the cause for a mal-functioning
catheter, e.g., a central line.
[0071] Yet another benefit is related to the fact that the guided
vascular access devices and the systems described herein may be
inserted into the existing healthcare workflow for placing
endovascular devices into the vasculature. More specifically,
embodiments of the invention provide new sensor based endovascular
devices, systems and methods for intravascular guidance and
placement of, for example, sensor based catheters and/or guide
wires. Then, the properly positioned sensor based endovascular
device is used to then guide the deployment of other endovascular
devices or facilitate the performance of other diagnostic or
therapeutic procedures in the body such as, for example: (a)
location of heart valves for replacement heart valve procedures;
(b) identification of the renal veins for therapy in those veins or
in the kidneys; (c) identification of renal veins and/or the
inferior vena cava for IVC filter placement; (d) location of
coronary sinus for placement of pacing leads or mitral valve
modification devices; and (e) location of pulmonary veins for
sensor placement and/or performance of therapy such as ablation
treatment for atrial fibrillation; as well as a wide variety of
other diagnostic or therapeutic procedures that would benefit from
the placement of device or performance of therapy at specific
locations in the vasculature identified by the sensor correlation
techniques described herein.
[0072] In some embodiments, the systems and methods of embodiments
of the inventive guidance system described herein are utilized to
locate, guide and position catheters and/or guide wires equipped
with sensors described herein within the vessels of the venous
system. The embodiments described herein may also be utilized in
the vessels of the arterial system as well. In one aspect, the
guided vascular access devices described herein may be used for the
guidance, positioning, and placement confirmation of intravascular
catheters used in a wide number of clinical applications. Exemplary
clinical applications that would benefit from embodiments of the
invention include the placement of, for example, central venous
access catheters (PICC), hemodialysis catheters and the placement
of catheters, positioning of endovascular devices in the
vasculature of the brain for treatment of stroke, placement of
leads or other brain based therapy or therapy devices or treatment
systems for percutaneous treatment of varicose veins. Moreover,
particular muscles or muscle groups may be selected for EMG
stimulation and/or sensor collection in support of one of more
methods and devices described herein where the EMG signals are used
to confirm and/or correlate a position in the vasculature. This
aspect may be particularly helpful when identifying portions of the
vasculature in the legs for localization of varicose veins,
localization of the femoral veins or positioning of a vessel
harvesting device within the great saphenous vein, for example.
[0073] While desiring not to be bound by theory, it is believed
that certain locations in the vasculature can be identified by
specific blood flow and electrogram patterns, electrogram signal
patterns and correlation between these blood flow patterns at those
locations. These patterns may be based on, for example, blood
pressure, Doppler blood flow measurements, and intravascular
electrocardiogram. Moreover, it is believed that the direction of
travel for a sensor equipped endovascular device can be determined
relative to the direction of blood flow by using the Doppler
effect, relative changes in the intravascular electrogram signal
and in the correlation between the blood flow and electrogram
information.
[0074] For example, in the case of a Peripheral Inserted Central
Catheter (PICC) line, by determining and real-time monitoring the
direction of the catheter movement in the blood vessels using the
sensors, techniques, data acquisition and processing described
herein (for example blood flow and electrogram information), a user
receives feedback on advancing a guided vascular access device to
allow the PICC to advance along a desired path from an insertion
vein into the vena cava and towards the sinoatrial node. The system
may also recognize unintended entry into other veins because of the
differences in flow patterns signals and electrogram signals or
other signals received from the sensors. As such, the system may
recognize unintended entry into the right atrium, inferior vena
cava, jugular vein, the subclavian vein. Additionally, the system
may detect when a sensor is against the vessel wall. By monitoring
the data acquired from sensors positioned on the endovascular
access device, the user can be notified when the device tip reaches
the ideal placement in the lower third of the superior vena cava,
at the caval-atrial junction and/or in the proximity of the
sinoatrial node. The system recognizes these locations of the vena
cava, and other vascular components, by analyzing sensor acquired
data to identify unique flow patterns and electrogram signatures
and to correlate these unique signatures in order to confirm
placement, location and/or guidance.
[0075] The ultrasound technology described herein is a non-imaging
ultrasound used in combination with intravascular electrograms, or
other physiological parameter sensor data. The unique flow patterns
may be discerned using non-imaging ultrasound and as such does not
require all the elements that make ultrasound imaging possible,
such as scanning with a moving transducer or working with phased
arrays and beam forming, and the like. As such, embodiments of the
present invention provide a vascular access and guidance system
with a hand-held, simple, inexpensive user interface. Non-imaging
ultrasound includes a number of various ultrasound techniques and
processing configurations, by way of non-limiting example: A-beam
ultrasound, Doppler ultrasound, continuous wave Doppler ultrasound,
pulsed Doppler ultrasound, color Doppler ultrasound, power Doppler
ultrasound, bi-directional Doppler ultrasound, and ultrasound
techniques that provide for the determination of velocity profile
based on correlation of blood flow and time.
[0076] One benefit of the methods, devices and systems described
herein is the use of a "multi-vector" or "multi-parameter"
approach. The multi-vector approach refers to the use of the blood
flow information, the electrical activity information and the
relationship between the two. The physiological information is
analyzed in order to identify the location in the vasculature where
the information was acquired. Because body functions are unique at
certain corresponding unique locations in the vasculature,
embodiments of the present invention can use measurements of the
body functions and detect location in the body.
[0077] In particular, the present invention describes the use of
the blood flow profile and of the intravascular ECG to detect the
proximity of the sinoatrial node and of the caval-atrial junction.
FIG. 17 illustrates the anatomical location of the caval-atrial
junction at the confluence between the superior vena cava (SVC) and
inferior vena cava (IVC just before entering the right atrium (RA).
FIG. 18 illustrates the anatomical location of the sinoatrial node
at the caval-atrial junction. The function of the vasculature and
the function of the heart are unique at the caval-atrial junction
both in terms of blood flow profile and of electrical activity of
the heart.
[0078] For example, the system according to the present invention
identifies the blood flow profile characteristic of the
caval-atrial junction and ECG waveform patterns characteristic of
the proximity of the sinoatrial node and, when both these patterns
are present, indicates to the user that the desired target location
has been reached. One benefit of this approach is that the blood
flow and the electrical activity are independent physiological
parameters and thus by considering them together, the accuracy of
the location information is significantly improved. In addition the
intravascular electrogram signal can be used for selective (gated)
acquisition and processing of the blood flow information, depending
upon the specific characteristics of the electrogram signal being
utilized. For example when the electrogram signal is produced by
the heart from the gating acquisition may be based on one or more
integrals of the heart cycle. This selective approach also
increases the accuracy of determining blood flow patterns
corresponding to locations in the vasculature.
Endovascular Member with Sensors for Guidance
[0079] FIG. 2 illustrates an endovascular device 150 having an
elongate body 105 with a proximal end 110 and a distal end 115.
There is a non-imaging ultrasound transducer 120 on the elongate
body 105. There is an atraumatic tip 121 on the endovascular device
150. The atraumatic tip 121 may also include an ultrasound lens.
The ultrasound lens may be used to shape the ultrasound signal
produced by the ultrasound transducer 120. In one aspect the
ultrasound lens is a divergent lens.
[0080] The endovascular device 150 also has an opening 182 in the
elongate body 105 and a lumen within the elongate body 105 in
communication with the opening 182 and the elongate body proximal
end 110. As illustrated, there may be one or more openings 182 in
communication with one or more lumens or tubes 183. Also shown on
the proximal end 110 are the various connections to the sensors and
lumens in the endovascular device 150. These connections are
conventional and may take any suitable form to connect the
endovascular device to the other guidance system 100 components
such as the processor, display or fluid delivery device. As such,
by using additional lumens or other access features, the elongate
body 105 or endovascular device 150 is adapted to deliver a therapy
to the patient such as by delivering drugs, therapeutic or
diagnostic agents through the openings 182 or between the inner and
outer tubes. In yet another alternative configuration, the elongate
body 105 or the endovascular device 150 is adapted to provide
endovascular access for another device.
[0081] The endovascular device 150 also illustrates how other
additional and optional sensors may be provided. Embodiments of the
endovascular device 150 may contain any of a number of different
sensors. The sensor is selected based on the physiological
parameter to be measured and used in the guidance, positioning and
correlation methods described herein. By way of non-limiting
example, the device may include an ultrasound sensor, a conductive
wire, a pressure sensor, a temperature sensor, a sensor for
detecting or measuring electrical potential and voltages and other
sensors suited to collecting physiological information and
providing information to the processor 140 for processing in an
algorithm or for other suitable form of analysis based on the
techniques described herein. The sensor-based endovascular device
150 can be used independently to deliver a payload into the
vasculature, e.g., a drug or to draw blood or it can be inserted
into the one of the lumens of another endovascular device, e.g., a
catheter. Then the entire assembly can be inserted into the
patient's body, e.g., for a PICC placement procedure, or through a
catheter 90 (see FIG. 4C).
[0082] Additionally or alternatively, the endovascular device 150
can be configured as any type of catheter, stylet, guidewire, an
introducer, a combination thereof or any other type of device which
allows for vascular access. The endovascular device and the
corresponding connection from the sensors to the proximal end can
either be fixed in the endovascular device, or pre-inserted and
removable after procedure, or reinsertable for location
verification post placement. In one embodiment the endovascular
device integrates a single lead electrode for electrical activity
monitoring. In a different embodiment, the endovascular device may
integrate several electrodes (leads), for example one at the very
distal tip of the endovascular member and one more proximal such
that the distal electrode can detect the electrical activity of the
heart while the more proximal electrode can serve as a reference
for measuring since the more proximal electrode is closer to the
patient's skin and further away from the heart. In addition to
providing electrical mapping, the lead/electrode can be used as a
steering element to steer and position the endovascular device as
illustrated in FIGS. 3A, 3B, 4A and 4B.
[0083] According to the embodiments of the present invention
physiological information is acquired by sensors and transmitted to
a processor. The processor uses algorithms which analyze and
process the sensor data to provide information on the location of
the sensor core assembly and of the corresponding endovascular
device in the patient's vasculature. Since high degree of accuracy
is desired, different types of physiological information, ideally
independent from each other, such as blood flow information and
electrogram information are used to accurately characterize the
direction of movement and location. In one aspect of the present
invention, the described clinical need is met by gathering
physiological information regarding blood flow using ultrasound and
regarding the electrical activity of the heart by acquiring
endovascular electrical signals.
[0084] By way of example, the endovascular device embodiments of
FIGS. 3A, 3B, 5A, 5B, consists of an elongate body 105 that may be
configured as any of a catheter, a stylet, or a guidewire that is
configured for endovascular access. Moreover, the catheter, stylet
or guidewire may be of the one part or two part construction
described herein.
[0085] The endovascular device 150 may be configured as a single
structure (FIGS. 3A, 3B, 4A, 4B, 5A and 5B, also be a removable
device or sensor core assembly may consist of a non-imaging
ultrasound transducer mounted at the end of a piece of tubing. The
tubing can be single or multi-lumen and can be made of any of a
variety of polymeric, or elastomeric materials. The lumens may be
used to support the sensors on the tubing or may be used for
delivery of therapeutic or diagnostic agents. One or more
physiological parameter monitoring sensors may be positioned on the
tubing as described herein. The endovascular device may have a two
part construction as shown in the illustrative embodiment of FIG. 2
where the ultrasound transducer is on a tube (an inner tube) within
another tube (an outer tube).
[0086] In the illustrative embodiment of FIG. 2, the inner tube
carries the ultrasound transducer. The outer tube, possibly a
multi-lumen tube, has a lumen for the inner tube. Additionally,
lumens 183 are provided to correspond to the openings 182. The
outer tube also supports the additional sensors (one sensor 186 is
shown). The wiring or other connections for the additional sensors
186 or electrogram lead may also be provided with their own lumen
or lumens. The proximal end 110 and the various leads and lumens
and other connections may be placed into a single connector used to
attach the endovascular device 150 to the other components of the
system 100.
[0087] Whether the endovascular device 150 is a single tube or a
multiple tube construction, the device include an additional sensor
186 on the endovascular device for measuring a physiological
parameter. In one aspect, the additional sensor is an optical
sensor and the physiological parameter is related to an optical
property detected within the vasculature. In another aspect, the
additional sensor is a pressure sensor and the physiological
parameter is related to a pressure measurement obtained within the
vasculature. In another aspect, the additional sensor is an
acoustic sensor and the physiological parameter is related to an
acoustic signal detected within the vasculature.
[0088] There is an endovascular electrogram lead 130 on the
elongate body 105 in a position that, when the endovascular device
150 is in the vasculature, the endovascular electrogram lead 130 is
in contact with blood. There are two endovascular leads 130 in the
illustrated embodiment of FIG. 2. As shown, there is an
endovascular electrogram lead 130 positioned at the elongate body
distal end 115.
[0089] As used herein, an electrogram lead 130 contains at least
one electrical sensing segment 135. The electrical sensing segment
135 is that portion of the electrogram lead 130 that is used for
detecting or sensing the electrical activity being measured. The
electrical sensing segment 135 could be a portion of the lead 130
that is not insulated, it could be a separate structure, like an
electrode, that is joined to the lead 130 or it could be a
structure within the endovascular device (see FIG. 5B). In one
aspect, the electrical sensing segment of an endovascular
electrogram lead is positioned within 3 cm of the elongate body
distal end 115. In another aspect, the electrical sensing segment
135 of an endovascular electrogram lead 130 is positioned within 3
cm of the non-imaging ultrasound transducer 120. As shown in FIG.
2, this aspect relates to the lead 130 that extends from the distal
end or to the spacing of proximally positioned endovascular lead
130. Additionally or alternatively, the electrical sensing segment
135 of an endovascular electrogram lead 130 is positioned proximal
to the non-imaging ultrasound transducer 120.
[0090] FIG. 2 also illustrates an endovascular device with a second
endovascular electrogram lead 135 on the elongate body 105. The
second endovascular lead is shown in a position that, when the
endovascular device 150 is in the vasculature, the second
endovascular electrogram lead 130 is in contact with blood.
Endovascular leads 130 (and/or the corresponding electrical sensing
segment or segments 135) may extend from the elongate body 105 as
shown in FIGS. 2 and 3A or may be integral to or within the
elongate body as shown in FIGS. 3B, 4A, 4B 5A, and 5B. In one
embodiment, the electrical sensing segment 135 of the second
endovascular electrogram lead 130 (the proximal electrogram lead
130 in FIGS. 2 and 4B) is positioned about 5 cm from the other
endovascular electrogram lead 130. Alternatively, electrical
sensing segment 135 of the second endovascular electrogram lead 130
is positioned about 5 cm from the elongate body distal end 115.
[0091] The use of two electrogram leads can be used to enhance the
measurement accuracy of the electrical signals being used in the
guidance system. In this regard, the electrical sensing segment of
the second endovascular electrogram lead is positioned at a
distance spaced apart from the endovascular electrogram lead so
that the second endovascular electrogram lead detects a baseline
electrogram signal when the endovascular electrogram lead is
detecting a target electrogram signal. In this way, the system may
rely completely on electrical signals completely within the
vasculature to obtain a baseline measurement thereby eliminating
the need for an external sensor as shown in FIG. 1. In this regard,
the electrical sensing segment of the second endovascular
electrogram lead is positioned such that when the electrical
sensing segment of the endovascular electrogram lead is positioned
to detect a targeted electrogram signal from the heart the
electrical sensing segment of the second endovascular electrogram
lead is positioned to detect a comparison baseline ECG signal.
Alternatively, the electrical sensing segment of the second
endovascular electrogram lead is positioned such that when the
electrical sensing segment of the endovascular electrogram lead is
positioned to detect a targeted electrogram signal from the brain
the electrical sensing segment of the second endovascular
electrogram lead is positioned to detect a comparison baseline EEG
signal. In another alternative, electrical sensing segment of the
second endovascular electrogram lead is positioned such that when
the electrical sensing segment of the endovascular electrogram lead
is positioned to detect a targeted electrogram signal from a muscle
the electrical sensing segment of the second endovascular
electrogram lead is positioned to detect a comparison baseline EMG
signal.
[0092] There are also embodiments where the spacing between the
electrogram leads is related to the target anatomy or anatomical
structures. In one example, the electrical sensing segment of the
second endovascular electrogram lead is positioned at a distance
related to the length of the superior vena cava such that when the
endovascular electrogram lead is in the superior vena cava the
second endovascular electrogram lead is outside of the superior
vena cava. Similarly, following the EEG and EMG examples above, one
lead would be near a target region of the brain or a muscle and the
second would be positioned so that it would detect baseline
electrical levels.
[0093] The conductive element for an electrogram lead can be made
up of any suitable biocompatible conductive material such as
stainless steel, a saline column or SMAs (smart memory alloys or
shape memory alloys), e.g., nitinol. The endovascular devices and
sensors described herein are suited and configured for use in the
vasculature and are thus sized and have appropriate finishes or
coatings to facilitate endovascular use. Typical diameters of the
conductive element are between 0.005'' and 0.010''. Typical lengths
of the conductive element or the endovascular device are between 1
and 8 feet.
[0094] Moreover, in some aspects, the conductive element is sized
and configured to perform multiple functions or functions in
addition to signal detection and transmission. For example, the
conductive element or electrogram lead may be used for steering,
tip positioning, and others. FIGS. 3A and 3B illustrate an
embodiment of an endovascular device 150 with an elongate body with
a proximal end and a distal end. There is a non-imaging ultrasound
transducer on the elongate body. There is an endovascular
electrogram lead on the elongate body in a position that, when the
endovascular device is in the vasculature, the endovascular
electrogram lead is in contact with blood. The electrical sensing
segment 135 is positioned to detect an electrogram signal. The
electrical sensing segment 135 is positioned in the window 170 and
can access blood. The window 170 is an opening into a lumen within
the elongate body that forms a sliding seal about the electrogram
lead 130. In this way, blood in contact with the window and the
lead is prevented from flowing down the interior of the elongate
body.
[0095] As best seen in FIGS. 3A and 3B, the endovascular
electrogram lead 130 is moveable from a stowed condition within the
elongate body (FIG. 3B) and a deployed condition outside of the
elongate body (FIG. 3A). As best seen in FIG. 3A, the electrogram
lead or conductive element can be deployed through a side opening
or window 170 in the sidewall of the elongate body 105. In one
embodiment, the window 170 is positioned at or near the distal end
of an endovascular member. As shown in FIG. 3A, the electrogram
lead 135 also serves the purpose of being able to distance the tip
115 or the ultrasound sensor 121 of the endovascular member away
from the inner wall of the blood vessel. In this way, the
endovascular electrogram lead is adapted for use to move the
ultrasound sensor away from a blood vessel wall.
[0096] The deployed shape of the electrogram lead 135 shown in FIG.
3A may include shapes that curve completely or partially about the
elongate body 105 and may be positioned proximal to the distal end,
span the distal end or be positioned distal to the distal end. In
one aspect the electrogram lead 135 is formed from a shape memory
metal or material that is appropriately pre-set into the desired
deployed shape. In one embodiment, the endovascular lead 130 is
made of nitinol. The endovascular lead 130 may also include an
atraumatic tip 139. The atraumatic tip 139 may be formed from the
electrogram lead (a curved end, shaped end or rounded end) or may
be a separate structure attached to the distal end to provide the
atraumatic capability.
[0097] The endovascular electrogram 130 may be used to perform a
number of additional and optional functions. As shown in FIG. 3B,
when the endovascular electrogram lead is in the stowed condition,
the lead curves the distal end 115. In this configuration, a
steering element (such as those shown in FIGS. 4A and 4B) may be
used to turn, twist or apply torque to the elongate body using the
endovascular lead 130. In this way, the endovascular electrogram
lead 130 may also be used for steering, placement or other guidance
requirements of the user.
[0098] FIGS. 4A and 4B illustrate alternative exemplary embodiments
of an endovascular device referred to as a sensor core assembly.
The sensor core assembly derives its name from the compact size
that allows it to be inserted into or ride along with within a
lumen on or in another endovascular device. In this way, the
functionality and advantages of the systems and methods described
herein may be applied to a wide variety of devices positioned
within or used within the vasculature. As such, the sensor core
assembly can be pre-inserted (if used for guidance and initial
placement) or later inserted (if used for position confirmation)
into one of the lumens (inside or alongside) of another
endovascular device, e.g. in into a PICC catheter.
[0099] The endovascular devices illustrated in FIGS. 4A and 4B also
illustrate a steering element 153 on the proximal end. The steering
element may be used to rotate one or both of the elongate body, a
steering element in the elongate body or an electrogram lead 130
configured for concurrent use as a steering element. In use, the
user would grasp the steering element 153 and manipulate as needed
to produce the desired movement of the elongate body, the distal
tip or the endovascular device. The steering mechanism 153 and the
endovascular lead 130 may also be sized and configured that the
lead, turned by the steering mechanism may apply torque or impart
rotation to the elongate body or otherwise facilitate manipulation,
steering or control of the endovascular device.
[0100] The embodiments illustrated in FIGS. 4A and 4B illustrate a
connector or hub 154 on the proximal end that provides an
appropriate and consolidated connection point for the sensors and
other components of the endovascular device to the guidance system
100. The connector 154 and steering device 153 may be adapted and
configured to allow relative movement between them so that the
steering element 153 may be used without interrupting the
connectivity provided by the connector 154.
[0101] FIG. 4C is a conventional catheter 90 with a body, a distal
end 95, a catheter hub 97 on the proximal end. A lumen 96 extends
from the distal end, though the body and hub into communication
with the tubes 92 and fittings 91a, 91b. The endovascular device
150 (FIGS. 4A and 4B) may be inserted directly into the patient
vasculature and guided as described herein to a target site.
Thereafter, the catheter 90 (or other device for placement) is run
over the device 150 until in the desired position. Alternatively,
the endovascular device 150 or sensor core assembly can be inserted
in the lumen of an endovascular device (lumen 96 of catheter 90)
which is then inserted into the patient's body and guided based on
sensor inputs from the endovascular device 150.
[0102] In another aspect, the elongate body 105 is itself
conductive using a metal wire or has integrated a conductive
element such that it can detect electrical activity of the body and
transmit resulting electrical signals to the proximal end of the
member. The proximal end of the conductive element can be attached
to a system for signal processing and graphical user interface. The
attachments for the various sensors and components of the
endovascular device 150 may be wired or wireless connections may be
used.
[0103] FIG. 5B is illustrates an endovascular device 150b with an
elongate body 105 with a proximal end and a distal end. There is a
non-imaging ultrasound transducer on the elongate body 120 and an
endovascular electrogram lead on the elongate body in a position
that, when the endovascular device is in the vasculature, the
endovascular electrogram lead is in contact with blood. In this
embodiment, the elongate body 105 comprises a coated metal braided
structure 172 as best seen in the cut away portion of FIG. 5B.
There is a coating 159 (typically an insulating coating may of a
biocompatible polymer) over the metallic or conductive braided
structure 172. A portion of the coating 159 on the metal braided
structure 172 is removed (providing a window 170). The exposed
metal braided structure (i.e., that portion exposed in window 170)
functions as an endovascular electrogram lead electrical sensing
segment 135. The remained of the braid 172 functions as the lead to
transmit the signals detected by the exposed section back to the
processor or other components of the guidance system 100.
[0104] Alternatively, as shown in FIG. 5B, the tube may be metallic
or metal braid encapsulated by polymeric material. Additionally or
alternatively, a polymeric material like PTFE or polyimide and a
polymeric compound, e.g., polyimide and graphite or glass fiber can
be used. A separate structure such as a spring, a wire or a mesh
wire, made with stainless steel or nitinol for example, may also be
inserted into or formed within the inner lumen of the sensor core
tube to provide additional column strength and resistance to
kinking or extreme bending to the sensor core tube. In addition,
the separate wire can also be used for conducting electrical
signals generated by the patient. FIGS. 5A and 5B demonstrate
examples of these designs.
[0105] In the embodiments illustrated in FIGS. 5A and 5B, the
sensor core assembly may contain a polymeric tube 159. The outer
diameter of the tube may be from 0.010'' to 0.030'', the inner
diameter from 0.008'' to 0.028''. The polymeric tube may be coated,
for example with PTFE. The transducer, which can be 0.010'' to
0.030'' in diameter is fixed at the distal end of the sensor core
assembly with Doppler-transparent adhesive or epoxy which can also
be used as a lens or a plurality of microlenses to optimize the
ultrasound beam profile.
[0106] At the distal end close to the transducer, there may be one
or multiple windows 170 or skived openings of 1 to 5 mm in length
and width each that provides the ability for an electrogram
element, e.g. the separate wire, to be in direct contact with
biological fluid, blood, or tissue. The separate wire or
electrogram lead can be made with any conductive material, e.g.,
nitinol, stainless steel, and is suitably connected to transmit
detected electrical signals to the proximal end of the sensor core
assembly and to components of guidance system 100. The separate
wire may consist of one continuous conductive element or several
conductive elements that are connected together.
[0107] In the embodiment in FIG. 5B the conductive element 130/135
is provided by a braid which is used to reinforce the shaft of the
endovascular device. The braid can be made of any conductive
material, e.g., stainless steel or nitinol, and can have any kind
of geometries and number of wires. The braid is exposed at the
distal end of the endovascular device to allow contact with blood
and therefore be capable of detecting electrical activity. In some
embodiments the braid servers as a reinforcement layer and
therefore is electrically isolated from both the inner and the
outer sides. In another embodiment, the tubing used for sensor core
assembly can be made with a sleeve which has a mesh in a braid or
coil form encapsulated by polymeric material. The sleeve may or may
not have a polymeric material only stem at its ends. The mesh can
be made with any conductive material, such as Nitinol or stainless
steel, and needs to be able to transmit electric signal from the
distal end to the proximal end of the sensor core assembly. The
mesh may consist of one or multiple types of conductive elements
and can be made with one or multiple conductive or non-conductive
materials. The mesh may also consist of one or multiple types of
continuous conductive element or several conductive elements that
are connected to each other. By removing some of the polymeric
material and exposing the conductive mesh to biological fluid,
blood or tissue, endovascular electrogram signal can be transmitted
through the mesh and the system can receive and interpret the
signals. A separate polymeric sleeve or other isolating material
can be used to isolate the wire attached to the Doppler sensor
(coaxial or twisted pair wire or grounded twisted pair wire or any
other type of conductive element) from contact with biological
fluid, blood or tissue. A Doppler-transparent atraumatic tip can
also be added to the distal end of the sensor core assembly. The
Doppler-transparent atraumatic tip can also be used as a
beam-shaping element for the ultrasound beam.
Endovascular Access and Guidance System
System Architecture
[0108] FIG. 6 illustrates a system 100 that can be used to guide
catheter placement using non-imaging ultrasound based blood flow
information and electrical activity of the body. In one particular
example, the system 100 is used to place an endovascular device 150
in the superior vena cava 14 using blood flow and ECG patterns and
relative to the sinoatrial node 8 using intravascular ECG. An
exemplary display 140 and/or user interface is shown in FIGS. 7, 8,
9, 13, 14A and 14D and is described below.
[0109] Returning to FIG. 6, the system 100 integrates a data
acquisition system, two DAQ cards, an isolation transformer and a
computing platform, e.g., a PC which has software loaded to process
the signals and display information on a screen. The data
acquisition system and the PC are powered from a common Isolation
Transformer or other suitable power supply. The data acquisition
system (1) is capable of acquiring ultrasound signals and
electrical signals generated by the body activity, such as
electrogram (ECG, EEG and/or EMG) including intravascular and
intracardiac electrocardiogram signals. A sensor-based endovascular
device 150 as described herein can be connected to the data
acquisition system (1). An additional ECG lead 112 can be attached
to the patient's skin (see FIG. 1) or provided by lead 130/135 for
collecting a reference signal. The optional speaker (11) is used to
optionally convert Doppler frequencies, i.e., blood velocities into
audible signals or to otherwise provide signals or instructions to
inform a user of the position of the device 150. One
analog-to-digital converter (8) is used to digitize ultrasound
signal information and transfer it to the processor 140 or other
suitable computing platform for processing. A second
analog-to-digital converter (9) is used to digitize electrogram
signals coming from the electrogram lead on the endovascular device
and from the reference electrode (either outside or inside the
vasculature). Other or additional A/D converters may be provided
based on the sensors used in the device 150.
[0110] The computing platform (4) can be a generic one like a
personal computer or a dedicated one containing digital signal
processors (DSP). The computing platform serves two purposes. It
provides the processing capabilities of the processor 140 that
allows data processing algorithms (5) to run. The various data
processing algorithms employed by the various methods of
embodiments of the current invention are described in greater
detail below. The other purpose of the computing platform is to
provide "back-end" functionality to the system 100 including
graphical user interface, data storage, archiving and retrieval,
and interfaces to other systems, e.g., printers, optional monitors
(10), loudspeakers, networks, etc. Such interfaces can be connected
in a wired or wireless configuration. Those of ordinary skill will
appreciate that the conventional components, their configurations,
their interoperability and their functionality may be modified to
provide the signal processing and data capabilities of the guidance
system 100.
[0111] FIG. 19 illustrates more detail of the functional blocks of
an exemplary Data Acquisition System 1 (from FIG. 6). These
components are those found in conventional ultrasound systems.
[0112] The signal flow path illustrated and described with regard
to FIG. 19 details how two different physiological parameters may
be sampled, acquired and digitalized for processing according to
the methods and systems described herein. While FIG. 19 may
specific reference to ECG and Doppler, it is to be appreciated that
the acquisition, conversion, processing and correlation described
herein may be applied generally to ultrasound and electrogram
signal combinations including a variety of different ultrasound
modes and various different types of sources of electrogram
signals. Moreover, ablation, acquisition, conversion, processing
and correlation steps, components and capabilities may be included
in the system 100 as needed depending upon the type and number of
sensors employed on the endovascular device 150
[0113] Returning to FIG. 19, the ultrasound transducer (TXD) 120
which can be driven as Doppler and A-mode imaging is attached to a
transmit/receive (T/R) switch to support pulsed wave operation. In
some configurations, the connection between transducer and system
may be optically isolated. The Pulser block generates the
ultrasound signal used to drive the transducer 120. Exemplary
signals are between 7-14 MHz. The Tx pulser table is firmware which
allows the system to define the exact shape of the pulse train
generated by the Pulser. The Programmable Gain (TGC) block
implements variable gain, in particular useful for time-depth gain
compensation. The Analog Filter (BPF) is a band-pass filter used to
filter out unwanted high and low frequency signals, e.g., noise and
harmonics. The Rx Gate and TGC Control block is used to select the
sample volume range (depth) and width, i.e., the target volume from
where the incoming (i.e. reflected) ultrasound signals are
acquired. In the case of Doppler, the sample volume range (depth)
and width defines the blood pool volume which is analyzed for
velocity information. In the case of A-mode acquisition, the range
extends from the transducer face to the entire available depth of
penetration, and maximum width. In addition the Rx Gate and TGC
Control is used to control the TGC block for the appropriate values
with respect to the range and width of the sample volume. The ADC
block converts the incoming analog signal into digital signal.
Typical values for the high frequency A/D conversion are 12 bit
depth of conversion and more than 100 MHz conversion rate. The FIFO
block contains ultrasound digitized data corresponding to the
sample volume as selected by the Rx Gate and TGC control block. The
System Interface block (CPU) allows for the following functional
blocks to be programmed algorithmically or by the user via a
general purpose computer (CPU): Tx Pulse and Pulser Table, Rx Gate
and TGC Control, and the Cos/Sin Table. The Cos/Sin Table is a
building block that is used for the quadrature demodulation of the
high frequency signal. The quadrature demodulation Cos/Sin table
can be implemented either in software as a DSP (digital signal
processor) function or as firmware in an FPGA (field programmable
gate array). The Mixer multiplies the incoming signal with qudratue
cos and sin signals to obtain 90 degrees phase shifted signals
which allow for extracting the Doppler frequency shift from the
incoming signal. The Mixer block can be implemented either as a DSP
or an FPGA function. The FIR (finite impulse response) filter is
used to filter the directional Doppler signals. An interface is
provided to transfer digital ultrasound and electrogram (or other
sensor) information to the host computer (CPU). The interface can
interface either as a standard USB interface (shown in FIG. 19), as
a network interface using TCP/IP protocols or any other kind of
digital bidirectional real-time interface. The Power Regulators
& Battery Charger provides power to the Acquisition System and
charge the batteries in a battery-powered configuration. The
Battery Monitor & Control block provides the interface (control
and monitor) of the battery and power by the host computer (CPU).
IN this example, the electrogram signal path consists of two
connectors to the endovascular device (leads 130/135) and/or a
reference lead 112, as needed. The connectors may be optically
isolated for patient safety. The ECG block consists of an amplifier
of ECG signals powered by the Isolated Power Supply. The ADC
digitizes the ECG signal with 8 to 12 bits at a sampling rate of
100 Hz to 1 KHz.
[0114] FIG. 20 illustrates an exemplary software block diagram 4
(FIG. 6) for providing the processing capabilities used by
embodiments of the present invention. The main software application
consists of several real-time threads running concurrently on the
host computer platform. The ACQ Universal Lib Agents controls the
acquisition of Doppler and ECG data. The Data Transfer Thread
distributes the data to the ECG Algorithm Thread, the Doppler
Algorithm Thread and the File Writer Thread. The Data Transfer
Thread also ensures synchronization between the ECG and the Doppler
data streams, such that, for example, ECG gated/synchronized
Doppler analysis can be implemented. The File Writer Thread streams
unprocessed real-time Doppler and ECG data to a storage device,
e.g., hard disk. The benefit of this approach is, that in playback
mode, i.e., when reading data from the storage medium through the
File Writer Thread, the data can be processed at a later time
exactly the same way it was processed at acquisition time. The ECG
and Doppler Algorithm Threads implement real-time feature
extraction and decision making algorithms as describes herein.
[0115] The ECG and Doppler Display Threads display ECG and Doppler
information on the graphical user interface (GUI) in real-time. The
Main GUI Thread is responsible for user interaction, system
settings, and thread and process synchronization and control. In
the embodiment illustrated in FIG. 20, the software applications
interact with a number of other components. An operating system,
e.g., Windows, Linux, or a real-time embedded operating system,
e.g. VxWorks provides the infrastructure for the application to run
and a number of services, e.g., interface to a database for patient
data repository. The ACQ Universal Library provides software
functions which control the data acquisition hardware. The ACQ USB
Driver or a TCP/IP network driver or any other kind of
communication driver controls the communication channel between the
Acquisition System (Module) and the host computer platform. Through
this bidirectional communication channel Doppler and ECG
information is transferred from the ACQ Module and control
information is transferred towards the ACQ Module.
Algorithms
[0116] In one embodiment, the system according to the current
invention uses two types of physiological parameters detected by
the sensor-based endovascular device 150 in order to determine the
location of the endovascular device 150 in the vasculature. In the
examples that follow, the parameters are ultrasound determined
blood flow patterns and intravascular electrocardiogram patterns.
FIGS. 7, 8, and 9 are views of a display 130 that illustrate blood
flow and electrocardiogram patterns at different locations in the
vasculature.
[0117] The display 130 illustrated in FIGS. 7, 8 and 9 includes: a
flow velocity profile output 705; a bar graph 710; a plurality of
indicators 715; and an electrogram output 720. The flow velocity
profile output 705 includes a curve 725 related to the flow away
from the sensor and a curve 730 related to the flow towards the
sensor. The relative power of these flows towards and away are
reflected in the bar graph 710. The bar graph 710 has an indication
740 for flow towards the ultrasound sensor and an indication 735
for flow away from the ultrasound sensor. The bar graph 710 may be
color coded. One color scheme would represent flow away as green
and flow towards as red. Based on the processing performed as
described herein, the system is able to determine several different
states or conditions for the endovascular device 150. The
indicators 715 are used to represent these conditions to a user
viewing the display 140. One indicator may be used to represent
movement of the device 150 in the desired direction. In the
illustrative embodiment, the arrow 745, when illuminated, indicates
proper direction of flow. The indicator may be colored coded, such
as green. One indicator may be used to represent improper or
undesired movement of the device 150. In the illustrated
embodiment, the octagon shape 750 when illuminated, indicates
direction to travel in an undesired direction. This indication may
be color coded red. Another indication may be provided to indicate
to the user that the system cannot determine or is unsure about
device 150 position or movement. The triangle 755 is used for this
indication. This indicator may be color coded yellow. Another
indicator may be used to inform a user that the system has
determined that the device 150 is in a position where the sensors
on the device are detecting signals of the target location when the
system detects, for example, blood flow patterns and electrogram
signals of the target location, the indicator 760 is activated.
Here, the indicator 760 is one or more concentric rings
representing bullseye. This indicator may also be color coded, such
as with the color blue. The electrogram output 720 displays the
electrogram signals detected by the electrogram leads used by the
system. The outputs displayed each of FIGS. 7, 8 and 9 correspond
to actual data and results obtained using a device and system as
described herein. For comparison, each of the ECG displays 720 are
the same scale to facilitate comparison of the ECG wave from at
each position. Similarly, the flow curves 725, 730 (and
corresponding relative sizes of the bar graph indications 735, 740)
are also representative of actual data collected using the devices
and techniques described herein.
[0118] The display 130 illustrated in FIGS. 7, 8 and 9 includes a
flow velocity profile 705 bar graph 710, indicators 715 and an
electrogram output 720.
[0119] FIG. 7 illustrates the blood flow velocity profile (705),
the intravascular ECG (770), indicator 715 (with 745 illuminated)
and bar graph 710 when the tip of the endovascular device 150 is in
or moving with venous flow towards the superior vena cava
(SVC).
[0120] When the device moves with the venous flow towards the
heart, the blood flow away from the sensor dominates the blood flow
towards the sensor as shown by the relative position of curves 725
and 730 and bar graphs 735, 740. The ECG 770 in FIG. 7 illustrates
the typical base line ECG expected in most locations when the
device 150 is away from the heart.
[0121] FIG. 8 illustrates the blood flow velocity profile (705),
the intravascular ECG (770), indicator 760 and bar graph 740 when
the tip of the endovascular device at the caval-atrial junction.
When the device 150 is positioned at a target location, correlation
of the various unique signatures of the target location may be used
to add confidence to the device position. When the device is at a
target site near caval-atrial junction then the blood flow
toward/away from the sensor are nearly balanced because of the
flows converging from the superior vena cava of the inferior vena
cava. This nearly equivalent flow toward/away is represented by the
proximity of the curves 725/730 as well as bars 735/740.
Importantly, the ECG 770 indicates the prominent P-wave that
indicates proximity of the ECG lead to the SA mode. The presence of
the larger P-wave is an example of a physiological parameter that
is used to correlate the flow information and confirm device
placement.
[0122] FIG. 9 illustrates the blood flow velocity profile (705),
the intravascular ECG (770), indicator 715 and bar graph 710 when
the tip of the endovascular device is in the internal jugular vein.
When the endovascular device 150 enters the jugular, the flow
towards the sensor now dominates the velocity profile as reflected
in the relative positions of the curves 730, 725 and the bars 735,
740 in bar graph 710. Additionally, the ECG wave demonstrates a
unique QRS polarity (i.e., the QRS complex is nearly equal negative
and positive). This distinctive ECG profile is used to confirm that
the device 150 has entered the jugular vein. Criteria for feature
extraction and location identification can be developed for both
the time and the frequency domain as well as for other
relationships that exist between criteria in time vs. frequency
domains.
[0123] FIG. 21 illustrates the flow chart 800 implementing an
exemplary algorithm according to one aspect of the present
invention. First, at step 805, Doppler and electrocardiogram/ECG
(ECO) signals are sampled at the desired frequency, typically
between 20 to 50 KHz/channel for the Doppler data and 100 Hz to 1
KHz for the ECG data. Next, at step 810, the ECG (ECO) and Doppler
data are transferred to the host computer memory. Next, at step
815, Doppler directional data (antegrade and retrograde or left and
right channel) and ECG data are separated at different memory
locations since they come packed together in the incoming data
stream from the sampler. Next, at step 820, the three data streams
(Doppler antegrade, Doppler retrograde, and ECG) are streamed to
the storage in sync. Next, at step 830, the algorithms identify the
R-peak in the ECG data stream and then locate the P-wave segment
within 400 to 600 ms to the left of the R-peak. If the answer to
block 840 is yes, then the ECG/ECO data is then appended to the
display buffer (step 845) and plotted on the graphical user
interface (step 850). If the answer in block 840 is no, then the
Doppler data corresponding to a desired period in the heart beat,
e.g., during the P-wave, during the QRS-complex, or during the
entire heart beat is processed as in steps 855, 860 and 865 through
FFT and filters and further described below. Based on the results
of processing, blood flow direction and tip location information
about the endovascular sensor-based device is presented on the
display and the Doppler information is plotted on the display.
[0124] In general, software controls to algorithms can be applied
to the frequency domain after performing a Fast Fourier Transform
(FFT) or in the time domain (No FFT). Typical numbers of points for
the FFT are 512, 1024, 2048, 4096. These numbers represent the
length of a data vector. The signal can be averaged over time or
over the number of samples both in time and frequency domains. The
on-line averaging uses a filter window of variable length (between
3 and 25 samples) to average along a data vector. The multi-lines
averaging computes the average of a selectable numbers of data
vectors. The can spectral power can be computed in frequency domain
from the shape of the power spectrum for each of the considered
signals (directional Doppler and ECG). The spectral power of the
directional Doppler spectra is used to differentiate between
retrograde and antegrade blood flow. Selective filtering of certain
frequencies is used to remove undesired artifacts and frequency
components, e.g., high frequencies indicative of a high degree of
turbulence. Selective filtering also offers the ability to look
consider certain frequencies as being more important than other in
the decision making process. For example the lowest and the highest
relevant frequency of the spectrum, i.e., the lowest and the
highest relevant detected blood velocity can be associated to
certain location in the vasculature and in the blood stream.
Threshold values are used to make decisions regarding the
predominant flow direction and the presence of the QRS-complex or
the P-wave. The threshold values can be computed using an
auto-adaptive approach, i.e., by maintaining a history buffer for
data and analyzing tendencies and temporal behavior over the entire
duration of the history data buffer.
[0125] Criteria useful in assessing location in the vasculature
based on ultrasound and ECG information are described below. Some
of the criteria which can be used to determine sensor location in
the vasculature from the blood flow velocity profiles are: a)
comparing energy, for example as measured by spectral power in
frequency domain, of each of the directions of bidirectional flow;
b) bidirectional flow patterns in lower velocity range to detect
the caval-atrial junction; c) pulsatility to detect atrial
activity; d) the highest meaningful average velocity of the
velocity profile and others described herein.
[0126] Some of the criteria which can be used to determine sensor
location in the vasculature from the intravascular ECG are: a)
peak-to-peak amplitude changes of the QRS complex or of the R-wave;
b) P-wave relative changes; c) changes in the amplitude of the
P-wave relative to the amplitude of the QRS complex or of the
R-wave; and others as described herein. The correlation between the
shape of the intravascular ECG waveforms and the shape of the blood
flow velocity profile as well as the correlation between the
relative changes of the two can also be used as criteria for
determining positioning, guiding or confirming sensor location in
the vasculature.
[0127] Returning to FIGS. 7, 8 and 9, in display 705, the
horizontal axis represents the Doppler frequency shift proportional
to the blood velocity and the vertical axis the amplitude of a
certain frequency, i.e., the power (or energy) or how much blood
flows at that particular velocity (frequency). The curve 725
illustrates the velocity distribution at the Doppler sensor
location of blood flowing away from the sensor. The curve 730
illustrates the velocity distribution at the Doppler sensor
location of blood flowing towards the sensor. Typically, the curve
725 is green and the curve 730 is red for applications where the
desired movement is towards the heart. Other color codes could be
used for a different vascular target. For the color-blind,
directions of flow can be indicated using symbols other than
colors, e.g., `+` may indicate flow away from the sensor and `-`
may indicate flow towards the sensor, or numbers may indicate
strength of flow. Scrollbars can also be used to indicate intensity
of bidirectional flow. Bar graphs 710, 735, 740 may also be used.
Another way to indicate direction of flow and to identify certain
flow patterns to the user is by using audible signals, each signal
being indicative of a certain flow, or in general, of tip location
condition. A green arrow (745), a green bull's eye (760), or a red
stop sign (750) can be used as additional indicators for flow
conditions and, in general, to identify the location of the sensor
in the vasculature. In ECG 770, the horizontal axis represents time
and the vertical axis represents the amplitude of the electrical
activity of the heart. The algorithms described herein may be
applied to the electrical mapping of the heart activity independent
of how the electrical activity was recorded. Devices described
herein may record intravascular and intracardiac ECG. Other methods
of recording ECG, for example using a commercially skin ECG monitor
(such as lead 112 in FIG. 1), are also possible and may be used as
described herein.
[0128] Referring again to FIGS. 7, 8 and 9, one criterion used for
correlating the Doppler frequency (velocity) distributions to the
anatomical locations refers to the spectral power or the area under
a specific Doppler frequency curve (the integral computed of the
frequency spectrum) in conjunction with the uniformity of
differences in frequencies over the entire frequency range. In FIG.
7 the sensor is positioned in the superior vena cava looking
towards the heart and with the main blood flow stream moving away
from the sensor towards the heart. The green area is larger than
the red one and, in this case, the curve 725 is above curve 730
over the whole range of Doppler frequencies (velocities). In FIG.
9, the catheter tip has been pushed into the jugular vein. The
blood is flowing towards the heart and towards the sensor located
at the catheter tip. The area under the red curve 730 is larger
than the area under the green curve 725 and the velocities in red
(towards the sensor) are larger than the velocities in green over
the entire range of velocities in this case. In each of FIGS. 7 and
9, the bar graph 710 indicates as well as the relative sizes of
flow towards and away from the sensor. Consequently, if the blood
velocity profile shows larger spectral power in one direction it is
inferred that this is the predominant direction of flow of the
blood stream.
[0129] Another criterion is related to the distribution of the low
velocities in the two directions (i.e., towards and away from the
sensor). In a vein, the blood velocities are different than, for
example in the right atrium. Therefore most of the relevant
spectral energy will be present in the low velocity range.
Typically, low blood flow velocity range is from 2 cm/sec to 25
cm/sec.
[0130] Another criterion is the similarity between the green
(toward) and the red (away) curves. At the caval-atrial junction
(FIG. 8) the green and red curves are almost identical with similar
areas (similar energy or the area under curves 725/730) and with
similar velocity distributions (similar velocity profiles or shape
of the curves 725, 730). This is indicative of the similar inferior
vena cava (IVC) and superior vena cava (SVC) flow streams joining
together from opposite directions when entering the right
atrium.
[0131] Another criterion is the behavior in time of the flow
patterns and signatures. In particular the behavior refers to the
difference between strongly pulsatile flow present in the right
atrium, in the heart in general as well as in the arterial flow
compared to the low pulsatility characteristic of venous flow.
[0132] Another criterion takes into account a periodic change in
behavior of the flow profiles with the heart rate. A stronger
periodic change with the heart rate or pulsatility is indicative of
the right-atrial activity.
[0133] Another criterion is the amplitude of the green and red
curves. The higher the amplitude at a certain frequency, the higher
the signal energy, i.e., the more blood flows at the velocity
corresponding to that particular frequency.
[0134] Another criterion is the amplitude of the highest useful
velocity contained in the green and red velocity profiles. Useful
velocity is defined as one being at least 3 dB above the noise
floor and showing at least 3 dB of separation between directions
(green and red curves). The highest useful velocity according to
the current invention is an indication of the highest average
velocity of the blood stream because the device according to the
present invention intends to measure volumetric (average)
velocities.
[0135] Another criterion is the temporal behavior of the velocity
profiles at a certain tip location. If the tip location is further
away from the heart, e.g., in the internal jugular vein, then the
predominant temporal behavior may be pulsatility due to respiration
of the main blood stream. FIG. 11 represents exemplary flow
patterns based on this concept. In the internal jugular vein the
main blood stream is represented by the red curve (blood flows
against the sensor). Closer to the heart and in particular in the
right atrium, the predominant temporal behavior is pulsatility
related to the heart beat.
[0136] Another criterion is related to the absolute and relative
changes of the P-wave at different locations within the
vasculature. As represented by ECG 770 in FIGS. 7, 8 and 9, the
P-wave dramatically increases at the caval-atrial junction (FIG. 8)
when compared to the P-wave in the superior vena cava (FIG. 7) or
the internal jugular vein (FIG. 9). Additional criterion relate to
the P-wave relative amplitude when compared to the QRS complex and
the R-wave.
[0137] FIG. 12 illustrates that even in the case of patients with
atrial fibrillation, the atrial electrical activity, which may not
be seen on the regular skin ECG becomes visible and relevant as the
intravascular ECG sensor approaches the caval-atrial junction. Both
the amplitude of the atrial electrical activity and its relative
amplitude vs. the QRS and R-waves change visibly at the
caval-atrial junction in the close proximity of the sino-atrial
node.
[0138] With reference again to FIGS. 7, 8 and 9, another criterion
is related to the absolute and relative changes of the QRS complex
and the R-wave at different locations. The R-wave and the QRS
complex dramatically increase at the caval-atrial junction (FIG. 8)
when compared to the waveforms in the superior vena cava (FIG. 7)
or the internal jugular vein (FIG. 9). Its relative amplitude to
the P-wave also changes dramatically. FIG. 12 shows that even in
the case of patients with atrial fibrillation, the R-wave and the
QRS complex change significantly as the intravascular ECG sensor
approaches the caval-atrial junction. Both the amplitude of the
R-wave and QRS complex and their relative amplitude vs. the P-waves
change visibly at the caval-atrial junction in the close proximity
of the sino-atrial node.
[0139] Any individual criterion and any combination of the above
criteria may be used to estimate location in the vasculature. A
database of patterns can be used to match curves to anatomical
locations instead of or in addition to applying the above criteria
individually.
[0140] FIG. 10 illustrates how the endovascular electrical signal
can be use to trigger and gate the processing of the ultrasound
signals. The electrical signal acquired from the endovascular
sensor is periodic and related to the heart cycle (10a). It is
similar in shape with a known diagnostic ECG signal. By analyzing
the waveforms, e.g., P-wave, QRS complex and the T-wave, a number
of events and time segments can be defined in the heart cycle. The
P-wave event occurs when the P-wave amplitude is at its peak.
The-R-wave event occurs when the R-wave amplitude is at its peak.
Other events can be defined, e.g., when the R-wave amplitude is one
third lower than the peak. Between such events time intervals can
be defined. T1 is the time interval between 2 consecutive P-waves
and indicates the heart rate. T2 is the time interval between two
R-waves and similarly indicates the heart rate. T3 is the time
interval between the P and the R waves. T4 is the time interval
between the R-wave and the subsequent P-wave. Other time intervals
can be defined, as well. These intervals can be defined in
reference to a peak value of a wave, the beginning or end of such a
wave, or any other relevant change in the electric signal. The
events defined in a heart cycle can be used to trigger selective
acquisition and/or processing of physiological parameters through
the different sensors, e.g., blood flow velocity information
through the Doppler sensor. The time intervals can be used to gate
the acquisition and processing of physiological parameters like
blood velocity, e.g., only in the systole or only in the diastole.
Thus more accurate results can be provided for guiding using
physiological parameters. Graphs 10b and 10c illustrate exemplary
ultrasound data triggered on the T3 interval.
[0141] FIG. 11 illustrates how the variations in blood flow as
identified by the Doppler signal can be used to trigger and gate
signal acquisition and processing based on the respiratory activity
of the patient. The flow patterns as indicated by the Doppler power
spectrum change with the patient's respirations. Certain cardiac
conditions like regurgitation also cause changes in the flow
patterns with respiration. Such changes with respirations can be
identified, in particular when the strength of a certain pattern
changes with respirations. These identified changes can then be
used to trigger and gate the acquisition and processing of
physiological parameters relative to the respiratory activity of
the patient. Thus more accurate results can be provided for guiding
using physiological parameters.
[0142] FIG. 12 illustrates how the relative changes in the QRS
complex can be used to identify proximity of the sinoatrial node
even in patients with atrial fibrillation, i.e., patients without a
significant P-wave detected by diagnostic ECG. In patients with
atrial fibrillation, the P-wave cannot be typically seen with
current diagnostic ECG systems (see (1)). Still changes, i.e.,
significant increases in the QRS complex amplitude as identified by
an endovascular sensor are indicative of the proximity of the
sino-atrial node (See (2)). In addition, an endovascular devices
can measure electrical activity which is not detected by a standard
ECG system, e.g., the atrial electrical activity in a patient
thought to have atrial fibrillation (See (3)). Such changes in the
waveform of the endovascular electrical signal can be used to
position the sensor and the associated endovascular device at
desired distances with respect to the sino-atrial node including in
the lower third of the superior vena cava or in the right
atrium.
Graphical User Interface
[0143] FIG. 13 illustrates elements of an exemplary display 130
configured as a graphical user interface (GUI) for a vascular
access and guidance system as described herein. The display 130 in
FIG. 13 integrates in a user-friendly way different guiding
technologies for vascular access: Doppler, ECG, audio, workflow
optimization, A-Mode imaging, for example. The Doppler window
presents the characteristics of the blood flow as detected using
Doppler or cross-correlation methods. The information can be
presented in either the time or the frequency domain. In the case
of bidirectional Doppler, the two directions can be represented on
a single display or on two different displays. Several Doppler
windows can be stacked and accessed though tabs in order to either
provide a history of the case or to access a template database.
Alternatively the history/template window can be displayed
separately on the instrument screen. The A-Mode Imaging window
presents ultrasound information in a graph of time (x dimension)
version depth (y dimension). The window gets updated regularly such
that the movement of the hand holding the A-Mode imaging device
appears to be in real-time. This increases the ability of hand-eye
coordination. Typically the origin of an A-mode single beam is on
top the screen and the A-Mode ultrasound flash light is looking
down. Another use for the A-Mode imaging display window is to allow
for imaging and identification of blood clots. The Guiding Signs
window consists of colored elements of different shapes that can be
turned on and off. For example when the Doppler window displays a
much larger curve than a red one, then the green light in the
Guiding Signs window is turned on and all other lights are turned
off. The red light on (and the others off) indicated that the
endovascular sensor is pointing in the wrong direction. A yellow
light on indicates that the signal is not strong/clear enough to
make a determination. The blue light on indicates that the sensor
senses blood flow characteristic of the caval-atrial junction.
[0144] The ECG window displays electrical signals detected by the
endovascular probe. The window can display single or multiple
electrical signals and one or more ECG windows may be displayed.
The programmable function keys are shortcuts to different system
functions. They can be accessed through the touch screen or
remotely via a remote control. Typical function keys would select
screen configurations and system functions or would provide access
to default settings. The Audio window presents either the Doppler
or the audio information received from the endovascular sensor. In
a preferred embodiment the audio window is similar to the interface
of a digital audio recorder showing the intensity of the channels
(flow away and towards the probe) on simulated LED bars of
potentially different colors. For the color blind numbers are also
displayed showing the average intensity of flow in each direction.
Alternatively, a single LED bar can be used, such that the
different blood flow intensity in each direction is shown at the
two extremities of the single LED bar potentially in different
colors. The System Control Unit provides control over the data
acquisition devices, system settings, information processing,
display and archiving. Any combinations of the above described
windows are possible and each window type can have multiple
instances.
[0145] Display windows can be repositioned and resized, displayed
or hidden. The screen layout is user configurable and user
preferences can be selected and archived through the System Control
Window. The System Control Window can display an alphanumeric
keyboard which can be used through the touch screen. Character
recognition capabilities can facilitate input using a pen. A touch
screen enables the user to directly access all the displayed
elements. The loudspeakers are used for the sound generated either
by the Doppler or by auscultation components. The sound system
provides for stereo sound and alternatively headphones can be used.
In the case of Doppler information, the audible Doppler frequency
shift corresponding to one blood flow direction, e.g., towards the
probe can be heard on one of the stereo speakers or headphones,
e.g., the left channel. At the same time, the audible Doppler
frequency shift corresponding to the other blood flow direction,
e.g., away from the sensor can be heard on the other of the stereo
speakers or headphones, e.g., the right channel.
[0146] The system can be remotely controlled, networked or can
transfer information through a wireless interface. An RFID and/or
barcode reader allows the system to store and organize information
from devices with RFID and/or barcode capability. Such information
can be coordinated with a central location via, for example, a
wireless network.
[0147] In many clinical applications, endovascular devices are
required to have the device tip (distal end) to be placed at a
specified location in the vasculature. For example CVC and PICC
lines are required to have their tip placed in the lower third of
the superior vena cava. However, for example due to lack of a
guidance system at the patient's bedside, users currently place the
catheters into the patient's body blindly, often relying on x-ray
to confirm the location of the catheter a couple of hours after
initial placement. Since the CVC or a PICC line can be released for
use only after tip location confirmation, the patient treatment is
delayed until after X-ray confirmation has been obtained. Ideally,
users should be able to place the catheter at the desired location
with high certainty and with immediate confirmation of tip
location. Building a user-friendly, easy-to-use system which
integrates electrical activity information with other types of
guiding information, devices and techniques described herein.
[0148] FIG. 14 provides exemplary display 140 with an easy to use
graphical user interface which combines location information from
the different sensors and displays graphical symbols related to the
location of the endovascular device. For example, if the
endovascular device is advancing towards the caval-atrial junction
a green arrow and/or a heart icon are displayed together with a
specific audible sound as shown in FIG. 14B. If the endovascular
device is advancing away from the caval-atrial junction then a red
stop sign and/or a red dotted line are displayed together with a
different specific audible sound as shown in FIG. 14C or 14D. If
the tip of the endovascular device is at the caval-atrial junction
than a blue or green circle or "bull's eye" is displayed together
with a different specific audible sound as shown in FIG. 14A. Of
course, any colors, icons, and sounds or any other kind of
graphical, alphanumeric, and/or audible elements can be used to
indicate the tip location.
[0149] While the simplified user interface is displayed all the
underlying information (Doppler, ECG, and others) can be digitally
recorded so that it can be used to print a report for the patient's
chart. Storing of patient information, exporting the data to a
standard medium like a memory stick and printing this information
to a regular printer are especially useful when the device and
system disclosed in the current invention are used without chest
X-ray confirmation to document placement at the caval-atrial
junction of the endovascular device.
Ultrasound and ECG Methods of Positioning Guided Endovascular
Devices
[0150] FIG. 15 illustrates an exemplary method 300 of catheter
placement. In this example, the method 300 describes how a user
would place a PICC catheter using a guided vascular device with
guidance information provided using blood flow information and ECG
signals provided by the system and processing techniques described
in greater detail in the current invention. This example is for
illustration purposes only. Similar conventional catheter, guide
wire or device introduction procedures, may be tailored for the
requirements of other therapeutic devices such as, for example, for
placement of hemodialysis catheters as well as for the placement of
laser, RF, and other catheters for percutaneous treatment of
varicose veins, among others described in greater detail below. The
progress of the device through the vasculature 4 the signals
produced by the system will also be described with reference to
FIG. 16.
[0151] While the techniques described herein may be practiced in a
number of clinical settings, the placement method 300 will be
described for bedside catheter placement. The workflow presented in
catheter placement method 300 begins with step 305 to measure
approximate needed length of catheter. This step is recommended in
order to verify the location indicated by the apparatus. This step
is currently performed by the medical professional in the beginning
of the procedure.
[0152] Next, at step 310, unpack sterile catheter with placement
wire inserted and the sensor attached. In a preferred embodiment,
the packaged catheter already contains a modified stylet with
Doppler and ECG sensors. Currently, some PICC catheters are already
packaged with stylets which are used by the medical professionals
to push the catheter through the vasculature. Unlike the device
embodiments of the present invention, conventional catheters and
the corresponding stylets do not contain sensors suited to the
multi-parameter processes described herein.
[0153] Next, at step 315, connect non-sterile user interface
housing by bagging it with a sterile bag and piercing it with the
connector end of the placement wire. In a preferred embodiment, the
catheter containing the stylet with sensor is sterile and
disposable while the user interface, control, and signal processing
unit is reusable and potentially non-sterile. If the unit is not
sterilized and cannot be used in the sterile field, it has to be
bagged using a commercially available sterile bag. The catheter is
then connected to the user interface unit by piercing the sterile
bag with the stylet connector. Alternatively, a sterile cord or
cable can be passed off the sterile field and subsequently attached
to a non-sterile control unit without having to puncture a bag.
[0154] Next, at step 320, press self-test button on the user
interface housing and wait to see the green LED blinking. Once the
sensor is connected the system can execute a self test protocol to
check connection and sensor. Of course, any colors, icons, and
sounds or any other kind of graphical, alphanumeric, and/or audible
elements can be used to indicate the proper connection.
[0155] Next, at step 325, insert catheter into the vessel. This
step is similar to the catheter introduction currently performed by
medical professionals. One preferred insertion point is the basilic
vein 6 as shown in FIG. 16.
[0156] Next, at step 330, hold in position until green light stops
blinking (e.g., becomes solid green light). Once the catheter is in
the vessel, it must be held in position for a few seconds or be
slowly pushed forward. This step ensures that the signal processing
algorithm can calibrate the data acquisition and pattern
recognition to the current patient data. At this step a baseline
ECG signal may be recorded and stored in memory. Additionally, the
processing system will analyze the sensor date to confirm that the
sensor is placed in a vein not an artery.
[0157] Next, at step 335, after receiving confirmation from the
system that the sensor/catheter has been introduced into a vein,
the user may start advancing the catheter and watch the green light
to stay on. If the green light is on, it means that blood flows
away from the catheter tip. This "green light" indication is the
desired indication while advancing the catheter/sensor to the end
position. FIG. 16 shows a correct position of the catheter in the
basilic vein marked "Green" and meaning that the green light is on
(along the dashed pathway).
[0158] Next, at step 340, if the light turns red, stop advancing
and pull the catheter back until the light becomes green again. The
light turns red when blood flows towards the catheter/sensor
instead of away from it. This means that the catheter has been
accidentally advanced into the jugular or other vein. In FIG. 16
this positioned is labeled "Red" and the catheter is shown in the
internal jugular vein. In this situation the blood stream flowing
towards the heart comes towards the device. In this situation the
catheter must be pulled back to position labeled "2" in FIG. 16 and
re-advanced on the correct path into the SVC. If accidentally the
catheter is facing a vessel wall and cannot be advanced, the light
turns yellow: position marked "yellow" in FIG. 16. In this
situation the catheter must be pulled back until the yellow light
is off and the green one is on again.
[0159] Next, at step 345, advance while green light on. The user
keeps pushing while the catheter/sensor remain on the proper path
toward the heart.
[0160] Next, at step 350, the user stops advancing when light turns
blue. As illustrated in FIG. 16 the light turns blue when the lower
third of the SVC has been identified. The light turns blue when the
processing system has identified the unique flow pattern or
physiological parameters (i.e., unique ECG wave form) corresponding
to the targeted placement region. In this illustrative method, the
unique nature of the flow signature in the junction of the superior
vena cava and the right atrium is identified and the blue indicator
light illuminated. Next, at step 355, the user may verify actual
length against the initially measured length. This step is used to
double check the indication provided by the device and compare
against the expected initially measured length for the target
position.
[0161] Next, at step 360, remove stylet and attached sensor.
[0162] Next, at step 360, peel away introducer and then at step
370, secure catheter.
[0163] In additional alternative embodiments, there is provided a
method for positioning an instrument in the vasculature of a body
by processing a reflected ultrasound signal to determine the
presence of a signal indicating a position where two or more
vessels join. This method may be practiced in any of a wide variety
of vascular junctions in both the venous and arterial vasculature.
One exemplary position where two or more vessels join occurs where
the two or more vessels include a superior vena cava and an
inferior vena cava. A second exemplary position where two or more
vessels join occurs where the two or more vessels include an
inferior vena cava and a renal vein. According to one embodiment of
the present invention, there is provided a method for positioning
an instrument in the vasculature of a body using the instrument
determine a location to secure a device within the vasculature of a
body; and securing the device to the body to maintain the device in
the location determined by the instrument. After the passage of
some period of time (as is common with patients who wear catheters
for an extended period of time, the instrument may be used to
calculate the current position of the device. Next, using the known
original position and the now determined current position, the
system can determine if the device has moved from the original
position.
[0164] It should be understood that various alternatives to the
embodiments of the invention described herein may be employed in
practicing the invention. For example if the target device position
where in the brain for example, then the processing algorithms and
outputs could be charged to indicate that movement into the jugular
is the correct direction (green indicator) and that movement
towards the heart would be an incorrect direction (red indicator).
The system indications and parameters can be altered depending upon
the location of and access route taken to various different target
sites in the vasculature.
[0165] Having described the various components and operability of
the inventive endovascular guidance system, numerous methods of
endovascular guidance are provided.
[0166] In one aspect, the method of positioning an endovascular
device in the vasculature of a body is accomplished by advancing
the endovascular device into the vasculature and then transmitting
a non-imaging ultrasound signal into the vasculature using a
non-imaging ultrasound transducer on the endovascular device. Next,
there is the step of receiving a reflected ultrasound signal with
the non-imaging ultrasound transducer and then detecting an
endovascular electrogram signal with a sensor on the endovascular
device. Then there is the step of processing the reflected
ultrasound signal received by the non-imaging ultrasound transducer
and the endovascular electrogram signal detected by the sensor.
Finally, there is the step of positioning the endovascular device
based on the processing step.
[0167] The method of positioning an endovascular device in the
vasculature of a body may also include additional or modified steps
according to the specific application or process being performed.
Numerous additional alternative steps are possible and may be used
in a number of combinations to achieve the guidance and positioning
results described herein. Additional steps may include verifying
that the length of the endovascular device inserted into the body
is equivalent to the estimated device length prior to the procedure
and/or inputting into the system the length of the endovascular
device inserted in the body. Additionally, the step of detecting an
endovascular electrogram signal with a sensor positioned on a
patient may be added. The sensor may be on the patient or a second
or additional sensor on an endovascular device. There may also be
added the step of comparing the endovascular electrogram signal
from the sensor on the device or patient to the endovascular
electrogram signal from the second sensor on the device.
[0168] The processing methods and algorithms may also be modified
or combined to identify important or unique signatures useful in
guidance, localization or correlation. The method may include
different or customized software or programming for processing
ultrasound and/or electrogram signal information. The processing
may include processing of reflected ultrasound signal to identify
the caval-atrial junction or to determine the highest average
velocity of a velocity profile. The processing may include
processing of the endovascular electrogram signal to determine:
peak to peak amplitude changes in an electrogram complex; peak to
peak amplitude changes of an QRS complex in an electrocardiogram;
peak to peak amplitude changes of an R-wave in an electrocardiogram
and or peak to peak amplitude changes of an P-wave in an
electrocardiogram and, additionally or alternatively, to use
electrogram information as a trigger to acquire and/or process
ultrasound information.
[0169] The processing methods and algorithms may also be modified
or combined to identify important or unique signatures to determine
the position of a guided endovascular device relative to anatomical
structures or positions in the body. Examples of these methods
include performing the processing step to determine the position of
the endovascular device relative to: the caval-atrial junction, the
sinoatrial node, the superior vena cava, the internal jugular vein,
and the subclavian vein.
[0170] The method of positioning an endovascular device in the
vasculature of a body may be further modified to include using the
endovascular device to determine a location to secure a device
within the vasculature of a body and then securing the endovascular
device along with the device to the body to maintain the device in
the location determined by the endovascular device. The method of
positioning an endovascular device in the vasculature of a body may
also include the steps of calculating a current position of the
device and then comparing the calculated current position of the
device to a location indicated by the processing step.
[0171] The steps of the method may be performed in any order or
repeated in whole or in part to achieve the desired positioning or
placement of the guided endovascular device. For example, the
method of positioning an endovascular device in the vasculature of
a body may include performing the processing step and the
positioning step until the endovascular device is positioned within
the right atrium relative to the coronary sinus. Alternatively, the
method of positioning an endovascular device in the vasculature of
a body may include performing the processing step and the
positioning step until the endovascular device is positioned within
the left atrium relative to a pulmonary vein. Alternatively, the
method of positioning an endovascular device in the vasculature of
a body may also include performing the processing step and the
positioning step until the endovascular device is positioned within
the aorta.
[0172] This aspect may be modified to include, for example, an
additional step of displaying a result of the processing step. The
processing step may also include information related to venous
blood flow direction. The venous flow direction may also include a
flow directed towards the sensor and a flow directed away from the
sensor. Additionally or alternatively, the result of the processing
step may also include one or more of information related to venous
blood flow velocity, information related to venous blood flow
signature pattern, information related to a pressure signature
pattern, information related to ultrasound A-mode information;
information related to a preferential non-random direction of flow
within a reflected ultrasound signal, information related to
electrical activity of the brain, information related to electrical
activity of a muscle, information related to electrical activity of
the heart, information related to the electrical activity of the
sinoatrial node; and information about the electrical activity of
the heart from an ECG.
[0173] In another aspect, the displaying step may also be modified
to include a visual indication of the position of the device. The
displaying step may also be modified to include a visual or color
based indication of the position of the device alone or in
combination with a sound based indication of the position of the
device.
[0174] The method of positioning an endovascular device in the
vasculature of a body may also be modified to include the step of
collecting the reflected ultrasound signal in synchrony with an
endovascular electrogram signal received by the sensor. Additional
alternatives are possible such as where the endovascular
electrogram comprises electrical activity from the heart, from the
brain or from a muscle. The collection step may be timed to
correspond to physiological actions or timings. For example, the
collecting step is performed in synchrony during the PR interval or
in synchrony with a portion of the P-wave.
[0175] Other portions of an EEG, ECG or EMG electrogram may also be
used for timing of collecting, processing and/or storing
information from device based or patient based sensors. In one
aspect of the method of positioning an endovascular device in the
vasculature of a body, the transmitting step, the receiving step
and the processing step are performed only when a selected
endovascular electrogram signal is detected. In one version of the
method, the selected endovascular electrogram signal is a portion
of an ECG wave. In another version of the method, the selected
endovascular electrogram signal is a portion of an EEG wave. In
still another version of the method, the selected endovascular
electrogram signal is a portion of an EMG wave.
[0176] The method of positioning an endovascular device in the
vasculature of a body may also include identifying a structure in
the vasculature using non-imaging ultrasound information in the
reflected ultrasound signal. In one aspect, the non-imaging
ultrasound information comprises using A-mode ultrasound to
identify the structure in the vasculature. In another aspect, the
non-imaging ultrasound information includes using Doppler
ultrasound information to identify a flow pattern in proximity to
the structure.
[0177] An another aspect of the method of positioning an
endovascular device in the vasculature of a body the processing
step is performed only on a portion of the reflected ultrasound
signals that correspond to a selected electrogram trigger signal.
This method may be employed, for example, when the selected
electrogram trigger signal is a portion of an ECG wave, a portion
of an EEG wave or a portion of an EMG wave.
[0178] In still other methods of positioning an endovascular device
in the vasculature of a body, the processing step may be modified
to include processing the reflected ultrasound signal by comparing
the flow energy directed away from the endovascular device to the
flow energy directed towards the endovascular device. In one
aspect, there is a step of selecting for comparison the flow energy
related to blood flow within the range of 2 cm/sec to 25
cm/sec.
[0179] In still other alternatives, the method of positioning an
endovascular device in the vasculature of a body includes a
processing step that has a step of processing the reflected
ultrasound signal to detect indicia of pulsatile flow in the flow
pattern. The indicia of pulsatile flow may be any of a number of
different parameters. The indicia of pulsatile flow may be: a
venous flow pattern; an arterial flow pattern or an atrial function
of the heart.
[0180] The method of positioning an endovascular device in the
vasculature of a body may also include modification to the
processing step to include the step of processing the endovascular
electrogram signal to compare the relative amplitude of a P-wave to
the relative amplitude of another portion of an electrocardiogram.
In one aspect, another portion of an electrocardiogram includes a
QRS complex. The processing step may also be modified to include
processing the reflective ultrasound signal to determine a blood
flow velocity profile and processing the detected endovascular
electrogram signal to determine a shape of the intravascular
electrocardiogram. The processing step may be further modified to
include the step of correlating the blood flow velocity profile and
the shape of the intravascular electrocardiogram to determine the
location of the endovascular device within the vasculature.
Pulmonary Artery Peripherally Inserted Central Catheter (PA-PICC)
and Pulmonary Artery Catheter (PAC)
[0181] A Pulmonary Artery Peripherally Inserted Central Catheter
(PA-PICC) and a Pulmonary Artery Catheter (PAC) are typically used
in procedures used to diagnose heart conditions, and measure
parameters used to determine the cardiac function of a patient.
These devices typically provide information regarding the central
venous, right heart, and pulmonary arterial blood pressures,
thermodilution measurements that are useful for calculating cardiac
output and related physiological parameters, access for drug
delivery, and blood sampling at various intervals along the length
of the catheter. In some embodiments, the PA-PICC or PAC balloon
catheter systems of the invention may also provide ECG information
along the pathway of the catheter from the central veins to the
pulmonary artery.
[0182] In some embodiments, as shown in FIGS. 22A and 22B, the
PA-PICC and/or the PAC systems comprise a balloon catheter 220
having a balloon 222 coupled to the catheter toward a distal end of
the catheter. In some embodiments, the balloon catheter comprises
elements of a conventional Swan-Ganz catheter, including a catheter
measuring at least 55 to 75 cm in length, or any other suitable
length, incremental markings to gauge insertion length (1-cm or
5-cm intervals, or any other suitable intervals), multiple lumens
with an end-port at a tip of the catheter, and spaced side-ports
which may be used for drug delivery, blood draws, mixed venous
blood sampling, thermodilution measurement, pressure measurements
at multiple locations simultaneously (may include pulmonary artery,
pulmonary capillary wedge pressure, right ventricular, and central
venous/right atrial pressure).
[0183] In some embodiments, as shown in FIGS. 22A and 22B, the
PA-PICC and/or the PAC systems may also include a Doppler sensor
(ultrasound transducer) 224 that is exposed at the distal tip of
the catheter. In some embodiments, the ultrasound transducer may be
coupled to a removal stylet. In some embodiments, one or more ECG
(electrocardiogram) sensors 226 and/or ECG leads that may exist as
part of the removable stylet or as a fixed member or members that
may be integrated with the catheter tip or shaft. Leads may be
spaced along the shaft of the catheter at various intervals to
allow for optimal ECG signal detection and discrimination to guide
catheter placement and to monitor cardiac electrical activity on a
continuous basis. Subtle changes in electrical activity may
correlate with normal and disease state physiology and changes in
cardiac functional status as reflected in cardiac output and blood
pressure fluctuations.
[0184] In some embodiments, the PA-PICC and/or the PAC systems may
be placed through the same access as a standard Swan-Ganz catheter.
The balloon catheter may be inserted in the same manner as a
typical PICC using the upper arm basilic vein as the access vein of
choice. In some embodiments, the balloon catheter may be inserted
with ultrasound guidance. After inserting the PICC 25 to 30 cm, the
balloon near the distal tip may be inflated with air and the
catheter may slowly advanced as would be the case for a Swan-Ganz
catheter inserted through a sheath into the internal jugular,
subclavian, or femoral vein. In some embodiments, the Doppler
sensor may activate during the placement process to identify the
right atrium, right ventricle, pulmonary artery, and wedge
position. Changes in the Doppler signature may indicate the
relative position of the Doppler sensor during tip advancement and
ultimate placement at the target. The ECG lead(s) may also indicate
tip position as the catheter is placed.
[0185] In some embodiments, once the wedge position is reached and
during times when the balloon is inflated for pressure
measurements, cessation of blood flow as determined by loss of
Doppler signal indicates that the wedge effect has been achieved.
In the standard Swan-Ganz system, changes in the blood pressure
measurements are used as an indication that flow within the
pulmonary artery branch has ceased. Sometimes this inference is not
entirely clear and the balloon may be inflated beyond the occlusion
diameter and in the process of over-inflation, the pulmonary artery
branch may be damaged or even rupture in rare instances with severe
untoward consequences to the patient. Sudden hemorrhage and death
have occurred from Swan-Ganz balloon-related trauma to the
pulmonary arterial vasculature (Bossert T, Gummert J F, Bittner H
B, Barten M, Walther T, Falk V, Mohr F W. Swan-Ganz
catheter-induced severe complications in cardiac surgery: right
ventricular perforation, knotting, and rupture of a pulmonary
artery. J Card Surg. 2006 May-June; 21(3):292-5.).
[0186] A PAC is generally used for diagnosis of heart conditions by
measuring various parameters used to determine a patient's cardiac
function. The PAC may be inserted percutaneously into a major vein
such as the jugular, subclavian, or femoral vein. The PAC is
inserted and advanced through the vasculature. In some embodiments,
once the PAC is inserted a distance into the vasculature, for
example inserted as far as the 30 cm mark on the catheter, if the
femoral vein is the access location, the balloon is inflated with
air. As the balloon is inflated, in some embodiments, changes in
the measured cardiac waveform can be monitored. The PAC may provide
circulatory pressure measurements including pulmonary artery
pressure, left ventricle, left atrium, right atrium, and pulmonary
artery occlusion pressure (also known as pulmonary artery wedge
pressure). A PAC catheter may also measure cardiac output
parameters, mixed venous oxygen saturation (SaO2), and/or oxygen
saturations in the right heart chambers to assess for the presence
of an intracardiac shunt for example. Using these measurements,
other variables can be derived, including pulmonary or systemic
vascular resistance and the difference between arterial and venous
oxygen content. In some embodiments, pulmonary artery occlusion
pressure (wedge pressure) may be measured when the PAC tip is
positioned in a pulmonary artery wedge position (typically in a
branch of the pulmonary artery) and the balloon is inflated. When
the balloon is inflated and blocking flow, the pulmonary artery
pressure tracing may disappear, and the resulting non-pulsatile
pressure tracing is called the pulmonary capillary wedge pressure
(PCWP), or pulmonary artery occlusion pressure. The PCWP is the
back pressure that is exerted from the left heart "filling
pressure".
Balloon Catheter System
[0187] As shown in FIGS. 22A and 22B, in some embodiments, the
balloon catheter system includes a catheter 220 adapted and
configured to be inserted into a patient's vasculature, an
expandable balloon 222 coupled to the catheter towards the distal
end of the catheter, and an ultrasound sensor 224 coupled to the
catheter distal to the balloon. The balloon catheter system may be
designed to detect parameters of a patient's cardiac function and,
more specifically, to detect parameters of a patient's cardiac
function while enabling the prevention of the balloon from over
expanding and distending a vessel of a patient. The balloon
catheter system may be alternatively used in any suitable
environment and for any suitable reason.
[0188] In some embodiments, the balloon catheter is a Swan-Ganz
catheter. The catheter in this embodiment may be at least 55 to 75
cm in length, or any other suitable length, having incremental
markings to gauge insertion length (1-cm or 5-cm intervals, or any
other suitable intervals). The catheter may include multiple lumens
with an end-port at a tip of the catheter, and spaced side-ports
which may be used for drug delivery, blood draws, mixed venous
blood sampling, thermodilution measurement, pressure measurements
at multiple locations simultaneously (may include pulmonary artery,
pulmonary capillary wedge pressure, right ventricular, and central
venous/right atrial pressure).
[0189] As shown in FIGS. 22A and 22B, in some embodiments, the
balloon 222 is expandable. As shown in FIG. 22A, the balloon has a
first configuration. The first configuration may be a fully stowed
configuration, or may alternatively be a partially inflated
position as shown in FIG. 22A. By partially inflating the balloon,
the blood flow within the vasculature of the patient may carry the
balloon catheter once inserted by pushing the partially inflated
balloon along with the blood flow. As shown in FIG. 22B, the
balloon is expandable such that it contacts the vessel wall,
thereby substantially stopping the blood flow through the
vessel.
[0190] As shown in FIGS. 22A and 22B, in some embodiments, the
balloon catheter system may further include an ECG sensor 226
coupled to the catheter distal to the balloon. In some embodiments,
the balloon catheter may include more than one ECG sensor. The ECG
sensors and/or leads may be spaced along the shaft of the catheter
at various intervals to allow for optimal ECG signal detection and
discrimination to guide catheter placement and to monitor cardiac
electrical activity on a continuous basis.
Methods for Evaluating Flow Characteristics
[0191] In some embodiments, as shown in FIG. 23, a method for
evaluating flow characteristics in a vessel of a patient includes
the steps of positioning a catheter having a balloon at a measuring
location within the vessel, step 230; transmitting an ultrasound
signal into the vessel while the balloon catheter is within the
measuring location, step 232; evaluating a reflection of the
ultrasound signal to determine a flow parameter within the vessel
while the catheter is in the measuring position, step 234;
expanding the balloon within the vessel at the measuring location,
step 236; and stopping the expanding step when the result of the
evaluating step is that the flow through the vessel is
substantially stopped, step 238. The method may be designed for
evaluating flow characteristics in a vessel of a patient and, more
specifically, for evaluating flow characteristics in a vessel of a
patient while enabling the prevention of a balloon from
over-expanding and over-distending a vessel of a patient. The
method may be alternatively used in any suitable environment and
for any suitable reason.
[0192] Step 230, which recites positioning a catheter having a
balloon at a measuring location within the vessel, may function to
advance the balloon catheter through the vasculature of a patient
to the measuring location. In some embodiments, the measuring
location may be within a pulmonary artery. In some embodiments, the
measuring location may be within a branch of the pulmonary artery,
while in some embodiments, the measuring location may be in a
pulmonary artery wedge position. The wedge position is a location
at which the balloon when expanded will obstruct the lumen of the
blood vessel and thereby halt blood flow through the vessel. In
some embodiments, the balloon may also be expanded in the superior
vena cava (SVC) and may act as a "sail" as the blood flow drags the
catheter through the right side of the heart until the balloon
lodges in a pulmonary artery branch. The site where the balloon
lodges may be the wedge position, and in some embodiments, may be
the position where the catheter tip may reside once the catheter is
secured at the skin insertion site, which in some embodiments, is
located in the neck.
[0193] In some embodiments, step 230, the positioning step, may
further include the steps of advancing the balloon catheter into
the vessel, transmitting an ultrasound signal into the vessel using
an ultrasound transducer on the balloon catheter, receiving a
reflected ultrasound signal with the ultrasound transducer, and
positioning the endovascular device based on the ultrasound signal.
In some embodiments, the ultrasound signal is reflected within the
vessel. This reflected signal may be received by an ultrasound
sensor on the balloon catheter. In some embodiments, the receiving
ultrasounds transducer is the same transducer as the transmitting
transducer. The reflected ultrasound signal may be used to
determine any number of characteristics or parameters that may be
useful in the guidance of the catheter during the positioning step.
These flow parameters may include, but are not limited to, blood
flow velocity, blood flow intensity, blood flow direction (blood
flow towards the transducer and/or blood flow away from the
transducer), blood flow signature pattern, pressure signature
pattern, spectrum characteristics, amplitude characteristics,
ultrasound A-mode information, or any other suitable parameters
and/or information. Ultrasound guidance of a catheter through the
vasculature of a patient is described in detail above.
[0194] Step 232, which recites transmitting an ultrasound signal
into the vessel while the balloon catheter is within the measuring
location, may function to send an ultrasound signal into a vessel
in order to detect characteristics about the vessel, and or the
blood flow through the vessel in and around the measuring location.
The ultrasound signal may be transmitted from an ultrasound
transducer coupled to the balloon catheter. In some embodiments,
the ultrasound sensor is coupled to the balloon catheter distal to
the balloon. The ultrasound signal transmitted into the vessel may
include a non-imaging ultrasound signal, an A-mode ultrasound
signal, and/or a Doppler ultrasound signal. In some embodiments,
the transmitting step is preformed throughout the expanding step,
or may alternatively be performed repeatedly after multiple
expanding steps, wherein the balloon may be expanded an amount each
time the expansion step is performed.
[0195] Step 234, which recites evaluating a reflection of the
ultrasound signal to determine a flow parameter within the vessel
while the catheter is in the measuring position, may function to
determine detect characteristics about the vessel, and or the blood
flow through the vessel from the ultrasound signal. In some
embodiments, the evaluating step includes receiving a reflected
ultrasound signal with an ultrasound transducer on the balloon
catheter. In some embodiments, the ultrasound transducer that
transmits the signal is the same transducer that receives the
signal. In some embodiments, the flow parameter determined is the
blood flow velocity and/or blood flow intensity within the vessel.
In some embodiments, the flow parameter determined is the blood
flow signature pattern within the vessel, while in some
embodiments, the flow parameter determined is a pressure signature
pattern within the vessel. The flow parameter determined may
alternatively be any other suitable parameter, and/or any suitable
combination of parameters.
[0196] Step 236, which recites expanding the balloon within the
vessel at the measuring location, may function to initiate and/or
complete the occlusion of the vessel with the balloon, in order to
block the flow through the vessel. Step 238, which recites stopping
the expanding step when the result of the evaluating step is that
the flow through the vessel is substantially stopped, may function
to stop the expansion of the balloon such that the balloon has
expanded to the point where it has just contacted the wall of the
vessel and/or substantially stopped the flow through the vessel but
has not yet over-expanded into the vessel wall. In some
embodiments, the balloon is preferably expanded to the point of
contacting the vessel wall and stopping the flow of blood through
the vessel, while the balloon is preferably not expanded to the
point where the balloon over-extends the vessel wall. In some
embodiments, the stopping step further comprises stopping the
expansion of the balloon when the ultrasound transducer receives a
reflected ultrasound signal that indicates that the flow through
the vessel has substantially stopped.
[0197] In some embodiments, the evaluating step determines the
blood flow velocity within the vessel and the stopping step further
comprises stopping the expanding step when the determined blood
flow velocity and/or blood flow intensity indicates that the flow
through the vessel has substantially stopped. In some embodiments,
the blood flow velocity and/or blood flow intensity will indicates
that the flow through the vessel has substantially stopped when the
velocity changes from a velocity in substantially a single
direction to a velocity in multiple directions. The velocity may
initially increase, and in some embodiments, may eventually drop to
zero.
[0198] In some embodiments, the evaluating step determines the
blood flow signature pattern within the vessel and the stopping
step further comprises stopping the expanding step when the
determined blood flow signature pattern indicates that the flow
through the vessel has substantially stopped.
[0199] In some embodiments, the evaluating step determines the
pressure signature pattern within the vessel and the stopping step
further comprises stopping the expanding step when the determined
pressure signature pattern indicates that the flow through the
vessel has substantially stopped. In some embodiments, the pressure
signature pattern indicated that the flow through the vessel has
substantially stopped by the pressure level dropping. In some
embodiments, the stopping step further comprises stopping the
expanding step when the result of the evaluating step is that the
pressure at the measuring location within the vessel has dropped
below the mean pulmonary arterial pressure. In some embodiments,
the stopping step further comprises stopping the expanding step
when the result of the evaluating step is that the pressure
signature pattern at the measuring location within the vessel is
consistent with a pulmonary capillary wedge pressure signature
pattern. In some embodiments, the pressure signature pattern
indicates a pressure lower than a pulmonary artery pressure and a
pressure more static than a pulmonary artery pressure. In some
embodiments, the stopping further comprises stopping the expanding
step when the balloon expanding pressure is at least equal to a
systolic pulmonary arterial pressure.
[0200] In some embodiments, as shown in FIG. 24 the method may
further comprise step 240, which recites deflating the balloon. The
balloon may be deflated to a stowed configuration, or may
alternatively be deflated to a partially inflated configuration. By
deflating the balloon, the blood flow past the balloon and through
the vessel may begin to return (i.e. increase from substantially
zero). In some embodiments, the balloon is preferably in the stowed
configuration while it is removed from the vasculature. It may be
easier to move the balloon through the vasculature while the
balloon is in a deflated configuration.
[0201] In some embodiments, the evaluating step may further
comprise step 242, which recites evaluating a reflection of the
ultrasound signal to determine a flow parameter within the vessel
after the balloon is deflated. In some embodiments, the flow
parameter determined may be the blood flow signature pattern within
the vessel, or any other suitable flow parameter or information. In
some embodiments, as the balloon deflates and decouples from the
vessel wall, the blood flow signature pattern may indicate the
resulting turbulent blood flow, and/or the general return of the
blood flow past the balloon. In some embodiments, the method may
further include step 244, which recites verifying that flow
parameter within the vessel determined after the balloon is
deflated is substantially similar to the flow parameter within the
vessel determined before the balloon is inflated. This step may
function to verify that blood flow has returned to normal flow
(i.e. baseline flow, in some embodiments measured before the
expansion of the balloon). This step may function as a safety
feature of the balloon catheter.
[0202] In some embodiments, as shown in FIG. 25 the method may
further comprise step 250, which recites detecting an endovascular
electrogram signal with a sensor on the endovascular device. In
some embodiments, the endovascular electrogram comprises electrical
activity from the heart, and in some embodiments, the electrical
activity of the heart is related to the sino-atrial node of the
heart. In some embodiments, ECG sensors may be spaced along the
catheter at various intervals to allow for optimal ECG signal
detection and discrimination to guide catheter placement and/or to
monitor cardiac electrical activity on a continuous basis. Subtle
changes in electrical activity may correlate with normal and
disease state physiology and changes in cardiac functional status
as reflected in cardiac output and blood pressure fluctuations. In
some embodiments, the timing of the expanding step may be based on
the electrogram signal. In some embodiments, the result of the
evaluating step is a combined evaluation of the ultrasound signal
and the electrogram signal.
[0203] In some embodiments, as shown in FIG. 25 the method may
further comprise step 252, which recites measuring a parameter used
to determine cardiac function. In some embodiments, the parameter
may be pulmonary artery occlusion pressure or any other suitable
parameter such as cardiac output. In some embodiments, the timing
of the measuring step is based on the detected electrogram
signal.
[0204] In some embodiments, as shown in FIG. 26, a method for
evaluating flow characteristics in a vessel of a patient includes
the steps of positioning a catheter having a balloon at a measuring
location within the vessel, step 260; transmitting a first
ultrasound signal into the vessel while the balloon catheter is
within the measuring location, step 261; evaluating a reflection of
the first ultrasound signal to determine a first flow parameter of
the vessel while the balloon is in a first configuration, step 262;
expanding the balloon within the vessel at the measuring location,
step 263; transmitting a second ultrasound signal into the vessel
during the expanding step, step 264; evaluating a reflection of the
second ultrasound signal to determine when the blood flow through
the vessel is substantially stopped, step 265; returning the
balloon to the first configuration, step 266; transmitting a third
ultrasound signal into the vessel after the returning step, step
267; and evaluating a reflection of the third ultrasound signal to
determine a third blood flow parameter of the vessel, step 268. The
method may be designed for evaluating flow characteristics in a
vessel of a patient and, more specifically, for evaluating flow
characteristics in a vessel of a patient while enabling the
prevention of a balloon from over-expanding and over-distending a
vessel of a patient. The method may be alternatively used in any
suitable environment and for any suitable reason.
[0205] Step 266, which recites returning the balloon to the first
configuration, may function to deflate the balloon such that it
returns to the first configuration. As described, the first
configuration may be a stowed configuration, or may alternatively
be a partially inflated configuration. By returning the balloon to
the first configuration, the blood flow past the balloon and
through the vessel may begin to return, and it may be easier to
move the balloon through the vasculature while the balloon is in
the first configuration. In some embodiments, the balloon is
preferably in the stowed configuration while it is removed from the
vasculature.
[0206] Step 267, which recites transmitting a third ultrasound
signal into the vessel after the returning step, may function to
send an ultrasound signal into the vasculature as the blood flow
past the balloon and through the vessel may begin to return. Step
268, which recites evaluating a reflection of the third ultrasound
signal to determine a third blood flow parameter of the vessel, may
function to detect a flow parameter of the blood flow through the
vessel and/or past the deflating/deflated balloon. In some
embodiments, the third flow parameter determined may be the blood
flow signature pattern within the vessel, or any other suitable
flow parameter or information. In some embodiments, as the balloon
deflates and decouples from the vessel wall, the blood flow
signature pattern may indicate the resulting turbulent blood flow,
and/or the general return of the blood flow past the balloon. In
some embodiments, the method may further include the step of
verifying that third flow parameter within the vessel determined
after the balloon is deflated is substantially similar to the first
flow parameter within the vessel determined before the balloon is
inflated. This step may function to verify that blood flow has
returned to normal flow (i.e. baseline flow, in some embodiments
measured before the expansion of the balloon). This step may
function as a safety feature of the balloon catheter.
[0207] In some embodiments, as shown in FIG. 27, a method for
evaluating flow characteristics in a vessel of a patient includes
the steps of positioning a catheter having a balloon at a measuring
location within the vessel, step 270; transmitting an ultrasound
signal into the vessel while the balloon catheter is within the
measuring location, step 271; detecting an electrogram signal while
the balloon catheter is within the measuring location, step 272;
evaluating a reflection of the ultrasound signal and the
electrogram signal while the catheter is in the measuring position,
step 273; expanding the balloon within the vessel at the measuring
location, step 274; stopping the expanding step when the result of
the evaluating step is that the flow through the vessel is
substantially stopped, step 275; and measuring a parameter used to
determine cardiac function, wherein the timing of the measuring
step is based on the result of the evaluation step, step 276. In
some embodiments, the result of the evaluating step is a combined
evaluation of the ultrasound signal and the electrogram signal. The
method may be designed for evaluating flow characteristics in a
vessel of a patient and, more specifically, for evaluating flow
characteristics in a vessel of a patient while enabling the
prevention of a balloon from over-expanding and over-distending a
vessel of a patient. The method may be alternatively used in any
suitable environment and for any suitable reason.
[0208] While preferred embodiments of the present invention have
been shown and described herein, it will be obvious to those
skilled in the art that such embodiments are provided by way of
example only. Numerous variations, changes, and substitutions are
incorporated herein by reference in their entirety. It is intended
that the following claims define the scope of the invention and
that methods and structures within the scope of these claims and
their equivalents be covered thereby.
* * * * *