U.S. patent number RE41,066 [Application Number 09/231,854] was granted by the patent office on 2009-12-29 for method and system for navigating a catheter probe.
This patent grant is currently assigned to Metronic Navigation, Inc.. Invention is credited to Wayne C. Haase, Michael A. Martinelli.
United States Patent |
RE41,066 |
Martinelli , et al. |
December 29, 2009 |
Method and system for navigating a catheter probe
Abstract
A system for navigating a catheter probe through a body cavity
includes a sensing coil affixed to a distal end of the probe.
Magnetic fields are projected into the body cavity to induce
voltage signals in the sensing coil that are sufficient to describe
the orientation and position of the probe. A set of magnetic coils
each generates a substantially uniform field in a single respective
dimension. The orientation angles of the sensing coil may be
determined from known values of the unidirectional fields and the
measured induced voltage signals. Gradient magnetic fields with
components in two dimensions are projected into the body cavity to
induce another group of voltage signals. The geometrical
intersection of constant voltage surfaces developed by certain
gradient fields that produce the measured induced voltage signals
is a set of lines on which the catheter is located. The point of
intersection of such lines yields the positional coordinates.
Inventors: |
Martinelli; Michael A.
(Winchester, MA), Haase; Wayne C. (Sterling, MA) |
Assignee: |
Metronic Navigation, Inc.
(Louisville, CO)
|
Family
ID: |
23947644 |
Appl.
No.: |
09/231,854 |
Filed: |
January 14, 1999 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
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Reissue of: |
09490342 |
Jun 14, 1995 |
05592939 |
Jan 14, 1997 |
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Current U.S.
Class: |
600/424;
128/899 |
Current CPC
Class: |
A61B
5/062 (20130101); A61B 34/20 (20160201); A61B
2034/256 (20160201); A61B 2034/2051 (20160201) |
Current International
Class: |
A61B
5/05 (20060101) |
Field of
Search: |
;600/117,424,407
;128/899,373 |
References Cited
[Referenced By]
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|
Primary Examiner: Smith; Ruth S
Attorney, Agent or Firm: Harness, Dickey & Pierce,
P.L.C.
Parent Case Text
.Iadd.CROSS-REFERENCE TO RELATED APPLICATIONS
This application is a reissue of U.S. Pat. No. 5,592,939 issued on
Jan. 14, 1997. The disclosures of the above patent is incorporated
herein by reference.
U.S. patent application Ser. No. 09/494,213 filed on Jan. 24, 2000
is also a reissue of U.S. Pat. No. 5,592,939 issued on Jan. 14,
1997 and claims benefit under 35 U.S.C. .sctn. 120 as a
continuation of this U.S. patent application Ser. No. 09/231,854
filed on Jan. 14, 1999..Iaddend.
Claims
What is claimed is:
1. A method of determining the location of a
magnetically-sensitive, electrically conductive sensing coil
affixed to a distal end of a catheter probe partially inserted into
a body cavity within a navigational domain, comprising the steps
of: inducing within said sensing coil a set of orientation signal
values each representative of an orientation of said sensing coil
and independent of a position of said sensing coil; determining the
orientation of said sensing coil using said induced orientation
signal values; inducing within said sensing coil a set of
positional signal values each representative of the position of
said sensing coil; and determining the position of said sensing
coil using said positional signal values and said determined
orientation.
2. The method as recited in claim 1, wherein the step of inducing
said set of orientation signal values comprises the steps of:
generating from outside said body a series of magnetic fields each
penetrating at least said navigational domain and characterized
substantially by a principal magnetic component in one axial
dimension and relatively smaller magnetic components in two other
axial dimensions.
3. The method as recited in claim 1, wherein the step of inducing
said set of positional signal values comprises the steps of:
generating from outside said body a series of magnetic fields each
penetrating at least said navigational domain and characterized
substantially by two principal gradient magnetic components in
respective axial dimensions and a relatively smaller magnetic
components in a third axial dimension.
4. The method as recited in claim 3, wherein said generating step
further includes the steps of: generating said fields to provide a
plurality of constant signal surfaces for the sensing coil such
that an intersection between two such surfaces with components in
the same axial dimensions produces a line along which said sensing
coil is located; wherein said two such surfaces are identified from
among said plurality of constant signal surfaces by their ability
to induce one of said positional signal values.
5. The method as recited in claim 4, further comprises the steps
of: weighting each line in accordance with a signal strength of
said corresponding constant signal surface; and determining an
intersection of said weighted lines.
6. The method as recited in claim 5, wherein six constant signal
surfaces are generated to produce three intersection lines.
7. A system for determining the location of a
magnetically-sensitive, electrically conductive sensing coil
affixed to a distal end of a catheter probe partially inserted into
a body cavity within a navigational domain, comprising: first
transmit means for projecting into said navigational domain
magnetic energy that is sufficient to induce signal values within
said sensing coil representative of an orientation of said sensing
coil and independent of the position of said sensing coil; second
transmit means for projecting into said navigational domain
magnetic energy that is sufficient to induce signal values within
said sensing coil representative of the position of said sensing
coil; and analysis means, coupled to said first transmit means and
said second transmit means, for determining the position and
orientation of said sensing coil from said induced signal
values.
8. A system for determining the location of a
magnetically-sensitive, electrically conductive sensing coil
affixed to a distal end of a catheter probe partially inserted into
a body cavity within a navigational domain, comprising: first
signal-inducing means for inducing within said sensing coil
orientation signals that are representative of the orientation of
said sensing coil; analysis means, coupled to said first
signal-inducing means, for determining the orientation of said
sensing coil using said induced orientation signals and independent
from a position of said sensing coil; second signal-inducing means
for inducing within said sensing coil position signals that are
representative of the position of said sensing coil; and analysis
means, coupled to said second signal-inducing means, for
determining the position of said sensing coil using said determined
orientation and said induced position signals.
9. The system as recited in claim 8, wherein the first
signal-inducing means comprises: field generation means for
successively generating magnetic field patterns projected into said
navigational domain, each characterized substantially by a
principal magnetic field component in one direction and relatively
smaller magnetic components in two other directions.
10. The system as recited in claim 9, wherein said field generation
means comprises a set of magnetic coils.
11. The system as recited in claim 10, wherein said magnetic coils
are disposed in a planar top of an examination deck upon which a
patient is disposed during a surgical procedure.
12. The system as recited in claim 10, wherein said magnetic coils
are disposed in a planar top and in rail members edge supported by
said planar top for an examination deck upon which a patient is
disposed during a surgical procedure.
13. The system as recited in claim 8, wherein the second
signal-inducing means comprises: field generation means for
successively generating magnetic field patterns each characterized
by a first and second gradient field component in respective
directions and a relatively smaller third component in another
direction.
14. The system as recited in claim 13, wherein the field generation
means comprises a magnetic coil assembly.
15. A method of determining the location of a
magnetically-sensitive, electrically conductive sensing coil
affixed to a distal end of a catheter probe partially inserted into
a body cavity within a navigational domain, comprising the steps
of: defining the location of said sensing coil with a set of
independent location parameters; and sequentially generating within
said navigational domain a sequence of magnetic fields for inducing
within said sensing coil a corresponding sequence of induced
signals each defined by an induced signal expression that
functionally relates said induced signal to certain ones of said
location parameters, such that said set of location parameters is
determinable by sequentially solving individual signal expression
groups each including certain ones of said induced signal
expressions and sufficient to represent a subset of said location
parameters.
16. The method as recited in claim 15, wherein said sequence of
magnetic fields comprises: a series of unidirectional magnetic
fields each characterized substantially by a principal magnetic
field component in one direction and relatively smaller magnetic
components in two other directions; and a series of gradient
magnetic fields each characterized by a first and second gradient
field component in respective directions and a relatively smaller
third component in another direction.
17. The method as recited in claim 16, wherein said signal
expression groups include: an orientation group including induced
signal expressions each functionally related to a respective one of
said unidirectional magnetic fields and an orientation of said
sensing coil, and independent of a position of said sensing coil;
and a position group including induced signal expressions each
functionally related to a respective one of said gradient magnetic
fields, the orientation of said sensing coil, and the position of
said sensing coil.
18. The method as recited in claim 17, wherein the step of
sequentially solving said individual signal expression groups
includes the steps of: initially solving the induced signal
expressions of said orientation group; and next solving the induced
signal expressions of said position group.
19. A system for determining the location of a
magnetically-sensitive, electrically conductive sensing coil
affixed to a distal end of a catheter probe partially inserted into
a body cavity within a navigational domain, comprising: means for
defining the location of said sensing coil with a set of
independent location parameters; and field generation means for
sequentially generating within said navigational domain a sequence
of magnetic fields for inducing within said sensing coil a
corresponding sequence of induced signals each defined by an
induced signal expression that functionally relates said induced
signal to certain ones of said location parameters, such that said
set of location parameters is determinable by sequentially solving
individual signal expression groups each including certain ones of
said induced signal expressions and sufficient to represent a
subset of said location parameters.
20. The system as recited in claim 19, wherein said sequence of
magnetic fields comprises: a series of unidirectional magnetic
fields each characterized substantially by a principal magnetic
field component in one direction and relatively smaller magnetic
components in two other directions; and a series of gradient
magnetic fields each characterized by a first and second gradient
field component in respective directions and a relatively smaller
third component in another direction.
21. The system as recited in claim 20, wherein said signal
expression groups include: an orientation group including induced
signal expressions each functionally related to a respective one of
said unidirectional magnetic fields and an orientation of said
sensing coil, and independent of a position of said sensing coil;
and a position group including induced signal expressions each
functionally related to a respective one of said gradient magnetic
fields, the orientation of said sensing coil, and the position of
said sensing coil.
22. The system as recited in claim 21, wherein said field
generation means comprises: analysis means for solving the induced
signal expressions of said orientation group; and analysis means
for solving the induced signal expressions of said position
group.
.Iadd.23. A method of determining the location of at least one
magnetically-sensitive, electrically conductive sensing coil
affixed to a medical device partially inserted into a body cavity
within a navigational domain, comprising the steps of: inducing
within the at least one sensing coil a set of induced signal values
corresponding to a set of location parameters, by sequentially
generating within the navigational domain (i) a series of
unidirectional magnetic fields, each characterized by a principal
magnetic field component in one direction, and relatively smaller
magnetic components in two other directions, and (ii) a series of
gradient magnetic fields, each characterized by a first and second
gradient field component in respective directions, and a relatively
smaller third component in another direction; wherein each of the
induced signals is defined by an induced signal expression that
functionally relates the induced signal to certain ones of the
location parameters, such that the set of location parameters is
determinable by sequentially solving individual signal expression
groups each including certain ones of the induced signal
expressions and sufficient to represent a subset of the location
parameters..Iaddend.
.Iadd.24. A method according to claim 23, wherein the signal
expression groups include (i) an orientation group including
induced signal expressions each functionally related to a
respective one of the unidirectional magnetic fields and an
orientation of the sensing coil, and independent of a position of
the sensing coil, and (ii) a position group including induced
signal expressions each functionally related to a respective one of
the gradient magnetic fields, the orientation of the sensing coil
and the position of the sensing coil..Iaddend.
Description
FIELD OF THE INVENTION
The present invention relates to catheter navigation systems and,
more particularly, to a method and system for determining the
position and orientation of a catheter probe being used during a
surgical procedure.
BACKGROUND OF THE INVENTION
Various configurations have been proposed to guide and detect a
catheter probe through the internal spaces of a patient undergoing
a surgical procedure. These proposed configurations are
characterized by several alternative approaches including, inter
alia, procedures for solving equations to determine unknown
location parameters, the generation and detection of magnetic
fields, and the use of sensing devices affixed to the catheter
probe.
U.S. Pat. No. 4,905,698 to Strohl, Jr. et al. discloses a locator
device external to a subject for generating an electromagnetic
field that projects into the subject. A catheter inserted into the
subject is fitted with a sensing coil at its distal end. The phase
of the voltage that is induced in the coil in response to the field
is compared to the phase of the generated field. When an in-phase
condition occurs, this is an indication that the locator is behind
the coil; alternatively, an out-of-phase condition indicates that
the locator is beyond the coil. Positions intermediate these two
rough approximations of the coil position are not determined other
than by a beeping indicator that signifies that this intermediate
positioning has been reached.
U.S. Pat. No. 4,821,731 to Martinelli et al. discloses an
electroacoustical transducer means secured to the distal end of a
catheter that is inserted into a subject for generating acoustical
pulses that propagate along an imaging axis and reflect from an
anatomical area of interest. The acoustic echoes are converted by
the transducer means into electrical signals representative of an
image of the anatomical area under reflection and the relative
position of the transducer means and angular orientation of the
sensing/imaging axis.
U.S. Pat. No. 4,642,786 to Hansen discloses a magnetic position and
orientation measurement system that determines the location of an
object in space with various configurations, each characterized by
the attachment of a retransmitter to the object consisting of
passive resonant circuits. The retransmitter is in a predetermined
position and orientation with respect to the object. A magnetic
field is generated at a resonant frequency of the retransmitter
which then retransmits a magnetic field for subsequent reception.
The position and orientation of the object may be calculated based
upon the induced signals as developed by the reception of the
retransmitted magnetic field. The original transmission and
reception may be implemented with an integrated transceiver,
separate transmitter and receiver elements, or a single transmitter
and an array of receiver coils.
U.S. Pat. No. 4,317,078 to Weed et al. discloses how the location
of a magnetically sensitive element may be determined by moving a
magnetic field source along specified reference axes to induce
signals in the sensor so as to identify a set of null points
representative of certain flux linkage values. The null point
locations are used to calculate the sensor position.
U.S. Pat. No. 3,868,565 describes a system where a magnetic field
is generated which rotates about a known pointing vector. The
generated field is sensed along at least two axes by a sensor
attached to the object to be located or tracked. Based upon the
relationship between the sensed magnetic field components, the
position of the object relative to the pointing vector can be
computed.
U.S. Pat. No. 4,173,228 to Van Steenwyk et al. discloses a catheter
locating system that includes a sensor attached to the distal end
of the catheter. An electromagnetic field is projected into the
body cavity with magnetic probe coils. The field is detected by the
sensor, which generates an induced signal whose magnitude and phase
are representative of field strength, separation of sensor and
probe coils, and relative orientation of sensor and probe coils.
The probe coil undergoes linear and rotational movement to identify
orientations and locations of the probe coil where minima and
maxima occur in the measured signal induced in the sensor. This
information is representative of the position and orientation of
the sensor.
U.S. Pat. No. 5,211,165 to Dumoulin et al. discloses a modified
catheter device that includes a small RF transmit coil attached to
its distal end. The transmit coil is driven by an RF source to
create an electromagnetic field that induces electrical signals in
an array of receive coils distributed around a region of interest.
Alternatively, the receive coils can be placed on the invasive
device and the transmit coils are distributed outside the patient.
A minimum of one transmit coil and three receive coils is necessary
to precisely determine the location of the invasive device. A
series of equations is developed to solve for the unknowns
x-y-z-.phi.-.theta..
PCT Application No. WO94/04938 to Bladen et al. describes how the
location and orientation of a single sensing coil may be determined
from induced signals developed in response to a sequence of applied
magnetic fields emanating from three groups of field generators
each including three mutually orthogonal coils.
The positioning methodology developed by Bladen et al. involves
calculating the distance from the sensing coil to each group of
field generators as a function of the induced voltage developed in
the sensing coil by the field generator. The distance calculation
is used to define the radius of a sphere centered on the respective
field generator. The intersection (i.e., overlap) of the spheres is
used to calculate an estimate of the sensor position, using the
spherical radius extending from the known location of the field
generators as the estimate for each generator.
The orientation algorithm of Bladen et al. develops general
equations for induced voltage including the entire set of unknown
variables (x-y-z location and .phi.-.theta. orientation). The
algorithm specifically solves for the orientation parameters by
substituting the measured induced voltage and the computed x-y-z
coordinates into the general induced voltage equation, and then
reduces the equations to the unknown variables .phi.-.theta..
In an alternative orientation algorithm described by Bladen et al.,
the induced voltage is treated as a vector quantity, allowing the
angle between the magnetic field at the generator and the radial
vector joining the sensor to the generator to be calculated with a
dot product computation. The angle between the radial vector and
the sensor axis can be determined from the computed field angle
using the dipole equations that define the generator fields. This
sensor angle and the radial position as determined by the position
algorithm together define the sensor position for use in the
alternative orientation algorithm. These values are used to compute
the angular orientation .phi. and .theta..
OBJECTS OF THE INVENTION
It is a general object of the present invention to obviate the
above-noted and other disadvantages of the prior art.
It is a more specific object of the present invention to provide a
catheter navigation system capable of determining the location of a
catheter probe.
It is a further object of the present invention to develop a
catheter navigation system employing a sensing coil affixed to the
end of a catheter probe for generating induced voltage signals that
are sufficient to describe the position and orientation of the
sensing coil.
It is a further object of the present invention to develop a
methodology for generating magnetic fields that are sufficient to
create a series of soluble mathematical expressions describing the
position and orientation of the sensing coil.
SUMMARY OF THE INVENTION
In one aspect of the present invention, an improved method of
determining the location of a magnetically-sensitive, electrically
conductive sensing coil affixed to a distal end of a catheter probe
partially inserted into a body cavity within a navigational domain
comprises the steps of: inducing within said sensing coil a set of
orientation signal values each representative of an orientation of
said sensing coil and independent of a position of said sensing
coil; determining the orientation of said sensing coil using said
induced orientation signal values; inducing within said sensing
coil a set of positional signal values each representative of the
position of said sensing coil; and determining the position of said
sensing coil using said positional signal values and said
determined orientation.
In another aspect of the present invention, an improved system for
determining the location of a magnetically-sensitive, electrically
conductive sensing coil affixed to a distal end of a catheter probe
partially inserted into a body cavity within a navigational domain
comprises: first transmit means for projecting into said
navigational domain magnetic energy that is sufficient to induce
signal values within said sensing coil representative of an
orientation of said sensing coil and independent of the position of
said sensing coil; second transmit means for projecting into said
navigational domain magnetic energy that is sufficient to induce
signal values within said sensing coil representative of the
position of said sensing coil; and analysis means, coupled to said
first transmit means and said second transmit means, for
determining the position and orientation of said sensing coil from
said induced signal values.
In another aspect of the present invention, an improved method of
determining the location of a magnetically-sensitive, electrically
conductive sensing coil affixed to a distal end of a catheter probe
partially inserted into a body cavity within a navigational domain
comprises the steps of: defining the location of said sensing coil
with a set of independent location parameters; and sequentially
generating within said navigational domain a sequence of magnetic
fields for inducing within said sensing coil a corresponding
sequence of induced signals each defined by an induced signal
expression that functionally relates said induced signal to certain
ones of said location parameters, such that said set of location
parameters is determinable by sequentially solving individual
signal expression groups each including certain ones of said
induced signal expressions and sufficient to represent a subset of
said location parameters.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 schematically illustrates a perspective view of a
patient-supporting examination deck in accordance with a preferred
embodiment of the present invention;
FIGS. 2A-C schematically illustrate a series of magnetic coil sets
for generating uniform fields in the x-, y-, and z-directions,
respectively, in accordance with a preferred embodiment of the
present invention, and which are configured within the deck of FIG.
1;
FIGS. 3 schematically illustrates a magnetic coil assembly for
determining the positional coordinates of the sensing coil in
accordance with a preferred embodiment of the present invention,
and which is configured within the deck of FIG. 1;
FIG. 4 is a flow diagram describing the location algorithm in
accordance with the present invention;
FIG. 5 schematically depicts the magnetic coil assembly of FIG. 3
to illustrate representative field patterns generated during an
excitation period;
FIG. 6 is a trace representatively illustrating surfaces of
constant signal from the sensing coil, as generated by the magnetic
assembly of FIG. 3;
FIG. 7 shows an upper plan schematic view of the magnetic assembly
of FIG. 3;
FIG. 8 schematically illustrates a perspective view of a
patient-supporting examination deck in accordance with another
embodiment of the present invention; and
FIGS. 9A-D schematically illustrate a series of magnetic coil
assemblies configured in the deck and rails of FIG. 8 for
determining the orientation and position of the sensing coil in
accordance with another embodiment of the present invention.
Throughout the drawings the same or similar elements are identified
by the same reference numeral.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention is directed to a method and system for
determining the location of a catheter or endoscopic probe inserted
into a selected body cavity of a patient undergoing a surgical
procedure. The location data is obtained from electrical
measurements of voltage signals that are induced within a sensing
coil affixed to the distal end of the catheter probe. These induced
voltage signals are generated by the sensing coil in response to
prespecified electromagnetic fields that project into the
anatomical region of interest which contains all prospective
locations of the catheters probe. The electrical measurements of
the induced signals provide sufficient information to compute the
angular orientation and the positional coordinates of the sensing
coil, and hence the catheter probe, which collectively define the
location of the sensing coil. The present invention is operative as
the patient is disposed on a patient-supporting examination
deck.
As used herein, "sensing coil" refers to an electrically
conductive, magnetically sensitive element that is responsive to
time-dependent magnetic fields for generating induced voltage
signals as a function of and representative of the applied
time-dependent magnetic field. The sensing coil is adaptable for
secure engagement to the distal end of a catheter probe.
As used herein, "navigational domain" refers to a fully enclosed
spatial region whose internal volume substantially encloses the
complete prospective range of movement of the sensing coil. The
navigational domain may be defined by any geometrical space but
preferably takes the form of a spherical volume. Under surgical
operating conditions, the navigational domain will correspond to an
anatomical region of the recumbent patient where surgical viewing
or investigation is desired (e.g., a diseased area of tissue or an
organ).
As used herein, "last navigational point" (hereinafter "the LNP")
refers to the most recently determined location of the sensing coil
before another iteration of the location algorithm is
performed.
As used herein, "uniform field" refers to a magnetic field having a
large magnetic field component in a specified axial dimension and
relatively smaller magnetic field components in the other axial
dimensions, and characterized by substantially uniform field values
throughout the navigational domain. In the x-y-z coordinate system
used herein, where the uniform fields of interest are the
x-directed, y-directed, and z-directed fields, the induced voltage
signals developed by such fields in the sensing coil are designated
V.sub.x, V.sub.y and V.sub.z, respectively. The term
"unidirectional field" is used interchangeably with "uniform field"
when appropriate.
As used herein, "unidirectional coils" refer to a magnetic assembly
that is operative to generate a uniform field (as defined above)
within the navigational domain. A distinct magnetic assembly is
employed for each uniform field. Although the unidirectional coils
described herein are preferably implemented with a collection of
appropriately designed magnetic coils, this implementation should
not be construed as a limitation of the present invention. Rather,
the unidirectional coils may be constructed from any magnetic
configuration that is sufficient to generate the uniform
fields.
As used herein, "gradient field" refers to a time-dependent
magnetic field having non-zero field components (i.e., components
with a high spatial gradient) in two of the three axial dimensions
for the coordinate system of interest (e.g., x-y-z system), and a
substantially zero component in the remaining axial dimension. For
mathematical purposes, a substantially zero component is generated
when its value is small compared to the net vector resulting from
the other two field components.
As used herein, "constant signal surface" or "constant voltage
surface" refers to a surface contour along which at every possible
point of location for the sensing coil the same induced voltage is
developed in the sensing coil.
As used herein, "delta coils" refers to a magnetic assembly for
generating a gradient field (as defined above) within the
navigational domain. As will become more apparent hereinafter, the
delta coils will typically be described in the context of delta
coil pairs including a long coil set and a short coil set each
generating gradient fields with components in the same axial
dimensions but whose magnetic field patterns are different. Each of
the long and short coil sets may be considered to generate a family
of constant signal or constant voltage surfaces from the sensing
coil within the navigational domain. Although the delta coils are
preferably implemented with an array of appropriately designed
magnetic coils (discussed below), this preferred implementation
should not serve as a limitation of the present invention as it
should be apparent to those skilled in the art that other magnetic
configurations may be used to adequately generate the gradient
fields.
As used herein, "magnetic look-up-table" (alternatively referenced
as "the LUT") refers to a database including the magnetic field
values at every x-y-z coordinate position within the navigational
domain for the unidirectional coils and delta coils used by the
present invention. Accordingly, input data consisting of an x-y-z
coordinate and a magnetic field identifier, which designates a
selected magnetic coil assembly, is indexed within the database to
a corresponding set of magnetic field values constituting the
output data. For the x-y-z coordinate system, the output data is
represented by the magnetic field variables H.sub.x H.sub.y H.sub.z
where the subscript indicates the axial dimension along which the
magnetic field value is being reported. The database is created
through a computational analysis of the magnetic field patterns
generated by the magnetic coil configurations used herein. The
mathematical model to develop the necessary formulae defining the
field patterns may be developed, for example, from near field
electromagnetic theory. An instructive text for facilitating such
an analysis is "Field and Wave Electromagnetics" 2nd edition
Addison Wesley (1989) by D. K. Cheng, herein incorporated by
reference. The database may be stored in any type of facility
including, inter alia, read-only memory, firmware, optical storage,
or other types of computer storage. Additionally, the database
information may be organized into any type of format such as a
spreadsheet. It should be apparent to those skilled in the art that
any suitable technique may be used to ascertain or record the
magnetic field values for the magnetic coil assemblies used
herein.
Separation of Variables Methodology
The mathematical construct underlying the present invention is a
methodology termed separation of variables. In accordance with this
methodology, appropriate equations are developed to isolate unknown
variables in such a manner that renders the equations uniquely
soluble. There are five unknown variables (.phi.-.theta.-x-y-z)
that define the location and orientation of the sensing coil. A
typical approach to solving for these variables would be to develop
a series of coupled non-linear equations expressing the
relationship among the variables. However, these equations are
generally not uniquely soluble, i.e., multiple solutions are
possible.
The mathematical approach used herein and predicated on the
separation of variables concept is directed to the development of a
series of signal expression statements functionally relating
induced voltage values to certain ones of the unknown location
parameters. The relationships defined by these expression
statements (i.e., induced voltage equations) are such that the
unknown variables are determinable by sequentially solving the
expression statements. In accordance with one aspect of the present
invention, a class of special magnetic fields is generated with
characteristic spatial structuring and shaping that is sufficient
to cause the variables (i.e., the location parameters) to separate
within these induced voltage equations so as to permit resolution
of the parameters x-y-z-.phi.-.theta. when the equations are
sequentially solved.
In particular, a series of substantially uniform fields is
successively generated in the x-, y-, and z-directions with the
group of unidirectional coils, thereby developing induced voltage
expressions (discussed below) involving only the variables .phi.
and .theta. independent of the unknown positional variables x-y-z.
This uncoupling of the variables .phi.-.theta. from the variables
x-y-z as accomplished by the substantially uniform fields is
specifically evident in the three induced voltage equations
expressed in two unknowns (i.e., .phi. and .theta.), which are
easily soluble.
The separation of variables methodology as applied to the
determination of the unknown positional coordinates x-y-z is
implemented with a sequence of gradient fields as generated by an
appropriate group of delta coils. Since the gradient fields have
components in only two of the axial dimensions, these fields induce
voltages in the sensing coil that are dependent upon the magnetic
field values in only these two dimensions at the sensing coil
position. As a result, each gradient field generates a family of
constant signal surfaces from the sensing coil, from which a
constant signal surface is identified for each gradient field that
produces the measured induced voltage in the sensing coil. The
intersection of two such constant signal surfaces is a line along
which the catheter is located. This intersection line is defined by
an expression in two of the unknown positional coordinates, wherein
the other equation parameters are known, i.e., the measured induced
voltage values, the magnetic field values at every x-y-z coordinate
for the coil groups (as supplied by the LUT), and the as-computed
.phi.-.theta. orientation. If an appropriate delta coil
configuration is used (e.g., three delta coil pairs), an
appropriate number of such intersection lines (e.g., three) may be
produced to sufficiently and uniquely resolve the x-y-z coordinates
(e.g., by calculating the intersection of such three intersection
lines).
Since there are five unknown variables to completely define the
catheter probe location, an equal number of independent equations
are needed to sufficiently describe its location. These unknowns
may be determined using one coil and five magnetic fields (as
described herein), two coils and three magnetic fields, or three
coils and two magnetic fields.
Overview of Location Algorithm
In accordance with the present invention, a location algorithm was
developed for determining the location of a sensing coil affixed to
the distal end of a catheter probe that is navigated through an
anatomical region of interest within a recumbent patient. The
location of the sensing coil is defined by an angular orientation
and positional coordinates. The angular orientation is represented
by an angle .phi. corresponding to the angle of departure from the
z-axis and an angle .theta. corresponding to the angle between the
x-axis and the projection onto the x-y plane of the vector
coincident with the longitudinal axis of the coil. In the
coordinate system for describing the present invention, the z-axis
coincides with the longitudinal dimension extending from the
patient's head to foot. The x-axis coincides with a lateral
dimension across the patient's body, and the y-axis is
perpendicular to the planar top of the pallet or examination deck.
These dimensions are identified as the patient is disposed in the
recumbent position on the pallet. As discussed below, the angular
orientation is determined from signals induced in the sensing coil
in response to a sequence of substantially uniform, unidirectional
fields generated successively within the navigational domain. The
positional coordinates are determined from signals induced in the
sensing coil in response to the gradient magnetic fields.
By way of background, the time-dependent magnetic fields projected
into the navigational domain induce voltages in the coil that are
representative of the orientation of the coil axis relative to the
lines of magnetic flux. The development of an induced voltage in an
electrical conductor in response to a changing magnetic field is
defined by Faraday's law. If one considers any closed stationary
path in space which is linked by a changing magnetic field, it is
found that the induced voltage V.sub.ind around this path is equal
to the negative time rate of change of the total magnetic flux
through the closed path. Denoting a closed path with the variable
C, the magnetic flus through C is given by, .PSI..intg..times.
.times.d ##EQU00001## where S is any surface bounded by the closed
path C. Thus, the mathematical statement of Faraday's law is
.delta..delta..times. .times..times..intg..times. .times.d
##EQU00002## Basically, the law states that a changing magnetic
field will induce an electric field which exists in space
regardless of whether a conducting wire is present. If a conducting
wire is present in the electric field, an induced voltage will
develop in the conductor. For a single-turn coil of wire of radius
d located in a uniform magnetic field B=B.sub.o sin.omega.t, where
the axis of the sensing coil is displaced at an angle .theta. with
respect to the lines of magnetic flux, the induced voltage measured
between the two open ends of the coil is expressed as:
.differential..differential..times..intg..times.
.times.d.differential..differential..times..pi..times.
.times.d.times..times..times. .times..theta..times. .times..times.
.times..omega..times. .times. ##EQU00003## .omega..times.
.times..pi..times.d.times..times..times. .times..theta..times.
.times..times. .times..omega..times. .times. ##EQU00003.2## This
relationship for a single coil may be used to determine the induced
voltage within a coil of N turns. Assuming that each turn of the
coil is separately and equally linked by the magnetic flux (e.g.,
in tightly wound coils), the induced voltage within the entire coil
assembly may be approximated as the summation of the induced
voltages developed in each turn. Accordingly, the total voltage
across the entire coil assembly is N times the induced voltage for
a single turn; hence, the induced voltage V.sub.ind is equivalent
to V.sub.ind=-N.omega..pi.d.sup.2B.sub.o cos.theta..omega.t
Clearly, the induced voltage in the sensing coil will vary with
changes in the angular orientation between the coil axis and the
direction of the magnetic field lines.
A useful reference frame for spatially conceptualizing the
interaction between the sensing coil and the magnetic fields is the
Cartesian coordinate system defined by mutually perpendicular axes
x-y-z. For purposes of illustration, a nonzero vector a is selected
to coincide with the axis through the sensing coil of the present
invention (hereinafter "coil axis").
The angles .alpha., .beta., and .gamma. that the vector a makes
with the unit coordinate vectors, , , and {circumflex over (k)},
respectively, are called the direction angles of a; the
trigonometric terms cos.alpha., cos.beta., and cos.gamma. represent
direction cosine values. Employing vector product notation, the
following expressions are developed: a
=.parallel.a.parallel.cos.alpha.; a
=.parallel.a.parallel.cos.beta.; and
ak=.parallel.a.parallel.cos.gamma.. Referencing the induced voltage
equations set forth above, these angles .alpha., .beta. and .gamma.
correspond to the angular displacement of the coil axis with
respect to uniform fields generated along the x-axis, y-axis, and
z-axis directions, respectively. Thus, the correspondence between
direction cosine expressions is as follows: cos.alpha. corresponds
to sin.phi.cos.theta.; cos.beta. corresponds to sin.theta.sin.phi.;
and cos.gamma. correspond to cos.phi.. Accordingly, the following
relationships illustrate the dependence of induced voltage on the
orientation parameters .phi. and .theta.:
V.sub.x.apprxeq.sin.phi.cos.theta.;
V.sub.y.apprxeq.sin.theta.sin.phi.; and V.sub.z.apprxeq.cos.phi.,
where the subscript indicates the direction of the magnetic field
that produced the measured induced voltage.
FIG. 4 is a flowchart detailing the location algorithm according to
the present invention and should be referenced in connection with
the discussion below.
As noted above, the last navigation point (LNP) refers to the x-y-z
positional coordinates of the sensing coil as determined by the
immediately previous computation cycle of the algorithm. For the
first cycle, the LNP is the center of the viewing field.
In accordance with a preferred embodiment of the present invention
for implementing the location algorithm, a magnetic assembly of
nine individual coil sets are used to generate the magnetic fields
sufficient to develop a corresponding set of nine induced voltage
signals that are fully representative of the location of the
sensing coil. The nine coil sets correspond to a group of three
unidirectional coil sets for generating uniform fields in the x, y,
and z-directions; a first delta coil group including a short coil
set at 0.degree. and a long coil set at 0.degree.; a second delta
coil group including a short coil set at 120.degree. and a long
coil set at 120.degree.; and a third delta coil group including a
short coil set at 240.degree. and a long coil set at 240.degree..
The angular designations associated with the delta coil groups
indicate the angle with respect to the z-axis of the coil dimension
that is perpendicular to the direction of elongation of the delta
coils. Accordingly, the three delta coil groups are arranged
pair-wise in a circular orientation about the y-axis at angles of
0.degree., 120.degree., and 240.degree..
The look-up-table (LUT) consists of a database containing the
magnetic field values (H.sub.x H.sub.y H.sub.z) at every x-y-z
coordinate location within the navigational domain for five coil
sets: the unidirectional coil sets for generating the uniform
fields in the x, y, and z-directions; the short coil (SC) set at
0.degree.; and the long coil (LC) set at 0.degree.. The magnetic
field value data for the short and long coil sets at 120.degree.
and 240.degree. may be obtained from the LUT by rotating the field
vectors for the long and short coil sets at 0.degree. by the angle
(i.e., .+-.120.degree.) appropriate for the given coil set. The
input data for the LUT consists of the x-y-z coordinates and a
designation of which coil set is being used to generate the
magnetic fields. In response to this input data, the LUT supplies
the magnetic field values H.sub.x H.sub.y H.sub.z at the selected
x-y-z coordinates for the designated coil set.
The LUT is present to speed up the operational sequence of the
location algorithm. Otherwise, an undesirable computational delay
exists if the required magnetic fields from the nine coil sets must
be individually calculated during each iteration of the algorithm.
By predetermining the magnetic field values and storing them in
LUT, the location algorithm need only access the LUT to retrieve
the appropriate field value without endeavoring into any complex
field analysis. At x-y-z coordinates other than those for which
magnetic field values are determined in the LUT, an interpolation
procedure is employed to calculate the field value.
Determining Angular Orientation of the Sensing Coil
The location algorithm of the present invention initially
undertakes a procedure to determine the angular orientation of the
sensing coil. An assumption is first made that the coil orientation
does not appreciably change during the period between cycle
computations. Accordingly, the magnetic field values corresponding
to the uniform field pattern at the LNP are used as an
approximation for the magnetic field values at the current but as
yet undetermined location.
The unidirectional coils are activated in succession, each
generating a substantially uniform field that projects into the
navigational domain and induces a corresponding voltage signal in
the sensing coil. The induced voltage signals are measured by an
appropriate detection unit coupled to a proximal end of the
catheter device where an electrical connection to the sensing coil
is established via suitable connection means extending along the
body of the catheter device.
The LUT is then accessed three times to acquire the magnetic field
values at the LNP for each of the three unidirectional coils. These
values and the measured voltage signals are then substituted into
the appropriate equations set forth below to solve for the unknown
variables .phi. and .theta. that define the coil orientation.
As a general principle, the voltage induced within the sensing coil
may be resolved into components along each of the axial dimensions
as determined by the extent to which the magnetic flux density is
developed along these axial dimensions. For example, a general
formula for the induced voltage produced by the unidirectional coil
which generates a substantially uniform field in the x-direction is
as follows: V.sub.x=H.sub.xxK sin.phi.cos.theta.+H.sub.yxK
sin.phi.sin.theta.+H.sub.zxK cos.phi. where magnetic field
intensity H is related to magnetic flux density by B=.mu.H and
K=.mu..sub.o .omega.N.pi.d.sup.2. The first subscript in the field
intensity term indicates the axial dimension along which the
magnetic field value was determined by accessing the LUT for the
given coil set at the LNP, while the second subscript indicates the
field-generating coil set. For an x-directed substantially uniform
field, the terms H.sub.yz and H.sub.zx are small compared to
H.sub.xx. Similar equations are developed below for the induced
voltages produced by the unidirectional coils successively
generating a y-directed and z-directed substantially uniform field:
V.sub.y=H.sub.xyK sin.phi.cos.theta.+H.sub.yyK
sin.phi.sin.theta.+H.sub.zyK cos.phi., and V.sub.z=H.sub.xxK
sin.phi.cos.theta.+H.sub.yxK sin.phi.sin.theta.+H.sub.zxK cos.phi..
The terms H.sub.xy and H.sub.zy in the equation for V.sub.y and the
terms H.sub.xz and H.sub.yz in the equation for V.sub.z are small
compared to H.sub.yy and H.sub.zz, respectively. After substituting
the measured values for the induced voltage signals, the equations
are simultaneously solved to determine the unknown variables .phi.
and .theta. defining the orientation of the sensing coil.
Determining Positional Coordinates of the Sensing Coil
By way of summary, the procedure for determining the positional
coordinates of the sensing coil in accordance with the present
invention first involves activating each delta coil in succession
and measuring the induced voltage thereby developed in the sensing
coil. Next, the LUT is accessed to obtain the magnetic field values
at the LNP for each specified delta coil. These magnetic field
values and the as-computed values for the orientation angles .phi.
and .theta. are then substituted into the appropriate induced
voltage equations to calculate for each delta coil the expected
value of the voltage signal induced in the sensing coil. This
expected value of the induced signal corresponds to a specific and
unique member of the family of constant signal surfaces of the
delta coils.
Based on the difference between the measured and expected values
for the induced voltage signals, a gradient is calculated
(representative of the rate of change of the induced signal) that
permits identification of the specific constant signal surface that
is responsible for generating the measured value of the induced
signal. This procedure is repeated for each delta coil.
For the activation of each delta coil group (comprised of one long
coil set and one short coil set), there is an intersection line
defined by the intersection of the two constant signal surfaces
(which were identified as developing the measured induced signal)
on which the sensing coil is located. The intersection of the three
such lines from the three delta coil groups uniquely provides the
x-y-z coordinates of the sensing coil. Although two such lines are
sufficient to describe the position of the sensing coil, greater
accuracy and more reliable performance in determining the catheter
position is achieved with three lines.
The following is a more detailed description of the procedure
summarized above for determining the positional coordinates.
The magnetic field pattern generated by the entire assembly of
short coil and long coil sets is characterized by a family of
surfaces of constant signal or constant voltage developed by the
sensing coil, each having non-zero components in two of the axis
directions and a small component in the remaining axis direction.
For example, the magnetic field surfaces generated by the short and
long coil sets oriented at 0.degree. relative to the x-axis have a
small value in the x-direction. The short coil positioned at
0.degree. (i.e., SC(0.degree.)) and long coil positioned at
0.degree. (i.e., LC (0.degree.)) are each independently activated.
The induced voltage in the sensing coil is measured for each coil
set. The LUT is then accessed to determine the magnetic field
values for the SC(0.degree.) and LC(0.degree.) coil set at the
LNP.
These magnetic field values (i.e., H.sub.x=small and non-zero
H.sub.y H.sub.z components) are used in conjunction with the
as-computed orientation angles .phi. and .theta. to calculate the
values of the induced catheter signals that would be expected from
such magnetic field values. The expected and measured induced
voltage values are compared, and the difference is used to identify
the constant signal surface from each of the SC(0.degree.) and
LC(0.degree.) coil sets that would have produced the measured
induced signals. The intersection of these identified magnetic
constant signal surfaces is a line parallel to the x-axis (thereby
resolving the y-z coordinates).
The aforementioned procedure involving the long and short coils
oriented at 0.degree. is iteratively repeated for a long and short
coil set oriented at 120.degree. (i.e., SC(120.degree.) and
LC(120.degree.)) and 240.degree. (i.e., SC(240.degree.) and
LC(240.degree.)).
More specifically, the coil sets SC(120.degree.) and
LC(120.degree.) are sequentially activated to induce corresponding
catheter signals in the sensing coil. In order to utilize the LUT
data on the coil sets oriented at 0.degree. for determining the
magnetic field components at the LNP generated by the coil sets
SC(120.degree.) and LC(120.degree.), a modified LNP is calculated
that is equivalent to the original LNP rotationally displaced by
120.degree.. The LUT is then accessed with the modified LNP to
determine the magnetic field values generated by the
SC(120.degree.) and LC(120.degree.) coil sets at the modified LNP.
The field vectors produced by the LUT for both the long coil and
short coil are then rotated (-120.degree.) to go from the modified
LNP to the actual LNP. Based upon these field values, a pair of
induced catheter signals are calculated that correspond to the
expected signal values arising from the magnetic field values for
the SC(120.degree.) and LC(120.degree.) coil sets. The difference
between the measured and expected induced catheter signals is used
to identify the magnetic constant signal surface for each of the
SC(120.degree.) and LC(120.degree.) coil sets that could produce
the measured catheter signal. The intersection of these identified
magnetic constant signal surfaces is a line oriented at 120.degree.
to the x-axis.
A similar procedure is used involving a modified LNP that is
rotationally displaced 240.degree. to simulate the magnetic field
patterns for the SC(240.degree.) and LC(240.degree.) coil sets
using the SC(0.degree.) and LC(0.degree.) field data. A line
oriented at 240.degree. to the x-axis is then identified along
which the catheter is located.
Each of the field lines oriented at 0.degree., 120.degree. and
240.degree. to the x-axis is weighted according to the strength of
the measured catheter signals. For example, a weak measurement
indicates a relatively imprecise identification of the intersection
line, resulting in a weaker weighting. This weighting reflects the
accuracy of the estimation used to determine the location of the
catheter with the specified coil set. An averaging technique is
used to compute a weighted estimate of the intersection of the
lines L(0.degree.), L(120.degree.) and L(240.degree.). The
intersection is the new value for x-y-z and will replace the x-y-z
of the old LNP to become the next LNP. The algorithm iteratively
repeats the aforementioned operations using the updated LNP to
arrive at the location of the sensing coil after each computation
cycle (e.g., every 0.1 s).
Magnetic Assembly for Determining Angular Orientation of Sensing
Coil
FIG. 1 schematically illustrates a perspective view of an
examination deck that facilitates implementation of the location
algorithm in accordance with a preferred embodiment of the present
invention, and which employs a magnetic coil assembly arranged in a
flat configuration. The examination deck includes a planar top
platform 10 suitable for accommodating a recumbent patient disposed
lengthwise on the planar top. The navigational domain is
illustratively depicted as the spherical volume 12 enclosing a
sensing coil 14 attached via suitable connection means 16 to an
external signal detection apparatus (not shown). The coil sets
embedded in platform 10 (and described in connection with FIGS.
2A-C and 3) are activated by a signal drive unit (not shown)
connected via line 18. The examination deck is preferably
constructed from a suitable magnetically-permeable material to
facilitate magnetic coupling between the embedded coil sets and the
overlying sensing coil.
Coil Set for Generating X-Directed Field
FIG. 2A schematically illustrates the unidirectional coil set for
generating a substantially uniform x-directed field throughout the
navigational domain 12. The coil set includes a first coil pair
with elements 20 and 24 and a second coil pair with elements 22 and
26, where the current flow as supplied by drive unit 28 is
indicated by the arrow symbol. Coil elements 20 and 22 are disposed
in the major surface of platform 10, while elements 24 and 26 are
disposed in the lateral walls of platform 10. Elements 24 and 26
are preferably used as compensation coils to substantially cancel
undesirable field components generated by elements 20 and 22 in the
y- and z-directions. The coils cumulatively generate a
substantially uniform x-directed field as indicated by
representative field line 27.
Coil Set for Generating Y-Directed Field
FIG. 2B schematically illustrates the unidirectional coil set for
generating a substantially uniform y-directed field throughout the
navigational domain 12. The coil set includes a coil pair with
elements 30 and 32 disposed in spaced-apart and parallel
relationship within platform 10, with the indicated current flow as
supplied by drive unit 34. The coils generate a substantially
uniform y-directed field as indicated by representative field line
33.
Coil Set for Generating Z-Directed Field
FIG. 2C schematically illustrates the unidirectional coil set for
generating a substantially uniform z-directed field throughout the
navigational domain 12. The coil set includes a first coil pair
with elements 36 and 40 and a second coil pair with elements 38 and
42, with the indicated current flow as supplied by drive unit 44.
Coil elements 36 and 38 are disposed in the major surface of
platform 10, while elements 40 and 42 are disposed in the lateral
walls of platform 10. Elements 40 and 42 are preferably used as
compensation coils (e.g., Cunard coils) to substantially cancel
undesirable field components generated by elements 36 and 38 in the
x- and y-directions. The coils cumulatively generate a
substantially uniform z-directed field as indicated by
representative field line 43.
The coil configurations shown in the Figures are only illustrative
and should not be construed as a limitation of the present
invention, as it should be apparent to those skilled in the art
that other coil configurations are possible within the scope of the
present invention provided such other configurations produce the
desired magnetic field patterns. A suitable connection means (not
shown) couples the sensing coil 14 to a signal measuring
device.
Magnetic Assembly for Determining Positional Coordinates of Sensing
Coil
FIGS. 3 and 5 show the coil configuration used to determine the
positional coordinates of the sensing coil in accordance with a
preferred embodiment of the present invention. The configuration
includes six coils grouped into three pairs of long and short delta
coils (50-52, 54-56, 58-60). The delta coils are mutually coplanar
and are disposed in the planar top of the examination deck
immediately beneath the recumbent patient. Interconnection means
between a signal drive unit (not shown) and the delta coil groups
is shown representatively for only coils 50-52.
The coils are preferably arranged in a circular orientation about
the y-axis such that there is an axis perpendicular to the
direction of elongation of the coils at 0.degree., 120.degree. and
240.degree. relative to the z-axis. The magnetic field generated by
the first group of long (50) and short delta coils (52) is shown
representatively by the field lines extending from the upper region
of the coils. The field lines from this delta coil group form the
family of constant signal surfaces shown within the navigational
domain 12. Superposition of the constant signal surfaces generated
by the long and short coils of a delta coil group produces a
fishnet pattern as shown in FIG. 6. The intersection of two such
constant signal surfaces generated by a short and long coil pair is
a single line represented by the dotted line 70.
A constant signal surface (72 and 74) is identified for each short
coil and long coil activation of a delta coil pair by determining
the surface that matches the induced signals developed in the
sensing coil. This procedure is repeated for the other two delta
coil pairs to produce two other lines comparable to line 70. The
intersection of these three lines determines the position of the
catheter.
FIG. 7 shows an upper plan schematic view of the entire delta coil
arrangement relative to an inner circular space representing the
projection of the navigational domain into the plane of the delta
coils. It is an object of the present invention to design coils
having high spatial gradience in two of the axis dimensions and a
substantially zero field value in the remaining axial dimension.
This particular design is accomplished by modifying the termination
points of the coils with compensation coils such that the modified
coil is effectively operative as an infinitely long coil. The long
coil sets are further compensated by a central "sucker" coil 88.
Accordingly, each of the long coils and short coils is modified by
representative compensation coils 80-82, 84-86, 88 and 90-94, 92-96
respectively, disposed at the indicated endpoints and center of the
corresponding delta coil. The long coil and short coil
configurations are shown schematically for only sets 50-52, but
similar configurations likewise exist for the coil sets 54-56 and
58-60 shown representatively as the indicated lines.
The quality of the coils, as measured by the degree of uniformity
of the uniform field coils or how close to zero is the field in the
non-gradient direction for the delta coils, determines the size of
the navigational domain over which the variable separation
technique for navigating the catheter will converge and therefore
be capable of initially finding the catheter, and hence be of
functional utility.
FIG. 8 schematically depicts an examination deck in accordance with
another embodiment of the present invention. The deck includes a
first rail member 100 and a second rail member 102 in opposed
spaced-apart relationship and attached to the platform along
respective supporting edges. The navigational domain is
illustratively depicted as the spherical volume 12. The deck
includes an apertured opening 104. Each rail member has an inner
wall and an outer wall. The railed configuration is characterized
by the embedding of coil sets in both the planar top and in the
rail members. The examination deck is preferably constructed from a
magnetically permeable material.
FIGS. 9A-C schematically illustrate the unidirectional coils for
implementing the railed configuration used in conjunction with the
examination deck of FIG. 8. The magnet assembly for the x-directed
unidirectional coil set is shown in FIG. 9A and includes two coil
elements 110 and 112 each embedded in a respective rail member.
Each coil pair is designed to project a substantially uniform field
in the x-direction throughout the navigational domain. FIG. 9B
schematically depicts the y-directed unidirected coils including
coil elements 114 and 116 each embedded in respective rail members,
and further including coil elements 118 and 120 embedded in the
planar top of the examination deck. FIG. 9C schematically depicts
the z-directed unidirected coils including coil elements 122-124 in
one rail member and elements 126-128 in the other rail member. The
current flow through each coil configuration is indicated by the
arrows. FIG. 9D shows the delta coil arrangement used in the railed
configuration. This arrangement is the same as used in the flat
configuration described above.
In accordance with another embodiment of the present invention, a
second sensing coil is used for stabilization purposes. Inaccurate
readings of the catheter probe location may occur from motion
artifacts due to breathing action, heart motion, or patient
movement. The stabilized location coordinates may be determined by
placing a second sensing coil on the sternum of the patient at a
known location within the navigational domain. The incremental
movement experienced by the second sensing coil due to motion
artifacts is detected and subtracted from the measured location
value of the probe to arrive at the actual location coordinates of
the probe. Further extensions of the present invention are possible
to facilitate multi-catheter applications by attaching an
additional sensing coil to the distal end of each additional
catheter.
Since certain changes may be made in the above apparatus and method
without departing from the scope of the invention herein described,
it is intended that all matter contained in the above description
or shown in the accompanying drawings shall be interpreted in an
illustrative and not in a limiting sense.
* * * * *