CA1259541A - Blood flow measurement catheter - Google Patents
Blood flow measurement catheterInfo
- Publication number
- CA1259541A CA1259541A CA000509795A CA509795A CA1259541A CA 1259541 A CA1259541 A CA 1259541A CA 000509795 A CA000509795 A CA 000509795A CA 509795 A CA509795 A CA 509795A CA 1259541 A CA1259541 A CA 1259541A
- Authority
- CA
- Canada
- Prior art keywords
- transducer
- blood vessel
- catheter
- elongate
- elongate body
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6886—Monitoring or controlling distance between sensor and tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
- A61B8/445—Details of catheter construction
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
- A61B5/6852—Catheters
- A61B5/6856—Catheters with a distal loop
Abstract
IMPROVED DOPPLER OUTPUT CATHETER
ABSTRACT OF THE DISCLOSURE
A catheter having a mechanism for positioning a doppler shift transducer carried by the catheter a-gainst a side wall of a blood vessel. A portion of the catheter near the distal end is adjustable for movement between a first position in line with the axis of the catheter and a second position in which such catheter portion is in the shape of an arc extending outward from the axis of the catheter such that the arcuate portion will wedge the body of the catheter against the other wall of the blood vessel. The adjustable portion can be manipulated using a mechanism near the proximal end of the catheter outside of a patient's body.
ABSTRACT OF THE DISCLOSURE
A catheter having a mechanism for positioning a doppler shift transducer carried by the catheter a-gainst a side wall of a blood vessel. A portion of the catheter near the distal end is adjustable for movement between a first position in line with the axis of the catheter and a second position in which such catheter portion is in the shape of an arc extending outward from the axis of the catheter such that the arcuate portion will wedge the body of the catheter against the other wall of the blood vessel. The adjustable portion can be manipulated using a mechanism near the proximal end of the catheter outside of a patient's body.
Description
5~5~1 IMP~OVED ~OPPLER OUTPUT CATHETER
This invention relates ~o doppler catheters and, in particular, to an improved catheter adapt~d to measure instantaneous blood flow.
Blood flow measurements are useful as an indi-cator of the cardiovascular control mechanism that regu-lates flow to all organs and tissues. The measurement of blood flow allsws an assessment of various interac-tions commonly used in modern medical practice to alter cardiac output and the functioning of the heart.
A catheter is an elongated tube-like device containing one or more hollow channels ("lumens") which is inserted into a blood vessel. Early catheters were developed to measure the pressure in an artery or vein.
These catheters were filled with fluid allowing trans-mission of pressure from a hole at the catheter's tip l"distal" end) to a pressure measuring device ~"manome-ter") at the end of the catheter outside the body (the"proximal" end). Later catheters incorp orated one or more transducers at the distal end which would transmit a signal down the catheter lumen to a measuring device at the proximal end. These catheters were developed to measure volumetric blood flow and blood flow velocity.
A balloon wedge pressure catheter is used to measure pressures on the left side of the heart with a catheter inserted into the right side of the heart.
This is done by advancing the catheter through the right side of the heart into the main pulmonary artery and into a pulmonary artery branch vessel. A balloon near the tip o the catheter is then inflated to block the vessel, thereby blocking pressures from the right side of the heart. The pressures measured by the tip of the catheter are that of the very distal pulmonary artery v~
This invention relates ~o doppler catheters and, in particular, to an improved catheter adapt~d to measure instantaneous blood flow.
Blood flow measurements are useful as an indi-cator of the cardiovascular control mechanism that regu-lates flow to all organs and tissues. The measurement of blood flow allsws an assessment of various interac-tions commonly used in modern medical practice to alter cardiac output and the functioning of the heart.
A catheter is an elongated tube-like device containing one or more hollow channels ("lumens") which is inserted into a blood vessel. Early catheters were developed to measure the pressure in an artery or vein.
These catheters were filled with fluid allowing trans-mission of pressure from a hole at the catheter's tip l"distal" end) to a pressure measuring device ~"manome-ter") at the end of the catheter outside the body (the"proximal" end). Later catheters incorp orated one or more transducers at the distal end which would transmit a signal down the catheter lumen to a measuring device at the proximal end. These catheters were developed to measure volumetric blood flow and blood flow velocity.
A balloon wedge pressure catheter is used to measure pressures on the left side of the heart with a catheter inserted into the right side of the heart.
This is done by advancing the catheter through the right side of the heart into the main pulmonary artery and into a pulmonary artery branch vessel. A balloon near the tip o the catheter is then inflated to block the vessel, thereby blocking pressures from the right side of the heart. The pressures measured by the tip of the catheter are that of the very distal pulmonary artery v~
2 ~s~3r~
bl c~llC}l whi(.-h i~. in di ?:~t communication with the pulmo-nary veins and which, in turn, reflect pressures on the left side of the heart.
Methods for measuring mean volumetric blood flow in man include thexmal dilution, dye dilution, and "Fick" oxygcn consumption methods. More recent devices have been developed to measure the instantaneous flow of blood in a vessel or artery. These include methods used to measure instantaneous flow by measuring changes in a concentric magnetic field across the blood vessel.
To generate the concentric magnetic field requires either a cuff surgically placed around the vessel or a catheter precisely centered in the middle of the blood vessel.
One method for centering an electromagnetic-type catheter is -to use an umbrella-like spring having a number of "V"-shaped spring elements with one end of the "V" coupled to the catheter and the other end coupled to a movable collar on the catheter. By moving the collar outwardly, the springs are made to expand and 20~ extend outward away from the catheter until the blood vessel walls are contacted. By using a number of these springs around the catheter, the catheter tip will be centered in the middle of the blood vessel. Such a centering device is disclosed in an article entitled "Registration of Phasic Changes of Bloodflow by Means of a Catheter-type Flow Meter," H. Piper, The Review of Scientific Instruments, Vol. 29, No. 11, p. 965 (Novem-ber, 1958).
Techniques for measuring volumetric blood flow require the determination of the diameter of the blood vessel in order to determine the total volume of blood flow through the vessel itself. One method of determining the diameter is similar to the above-de-scribed centering device. A number of hinged braces near the end of a catheter tip are extended outwardly when a cuff to which they are attached slides along the catheter length. When these braces contact the blood ~5~
vesscl wal~s, a signal proportional to the diameter of the blood vessel is produced and sensed. Such a mecha-nism is disclosed in an article entitled "Catheter-Tip Gauge for Measllring Blood Flow Velocity and Vessel Di-ameter in Dogs," Piper and Paul, Journal of Applied Physiology, Vol. 24, No. 2, p. 259 ~February, 196~).
Positioning problems may arise when a flow transducer is desired to be placed at the entrance to a small blood vessel branching off of a larger blood ves-sel. One method for accomplishing this involves attach-ing a wire to the end of the catheter similar to the bow string of a bow and arrow set. The transducer is placed at the center of that portion of the catheter directly opposite the wire that will be bowed. The catheter is then inserted into the main blood vessel until the transducer is adjacent to the entrance of the smaller blood vessel. The wire can then be pulled, thereby bowing the catheter and forcing the transducer against the entrance to the smaller blood vessel. See 20~ "An Electromagnetic ~atheter-Flow Meter," Kolin and Archer, Circulation Research, p. 889 (December, 1967).
A doppler ultrasonic technique for measuring blood flow velocity uses a transmitter to transmit ul-trasound across a blood vessel and a receiver to detect the change in frequency and phase shift of the reflected ultrasound signals. The measured frequency change is due to the movement of the blood cells which reflect the signals ("Doppler effect").
In one type of doppler flow meter ("continuous wave"), two transducers are used. One transducer con-tinuously transmits ultrasound signals and the other continuously receives the reflected ultrasound signals.
A weighting technique can then be used with readings from this type of doppler flow meter to determine the average velocity.
A pulsed-wave doppler technique uses a single crystal transducer with the received signal being sampled - ~25~
at c~rtain s,pccified intervals. These intervals corre-spond to different fixed posi-tions across the blood vessel. The intervals are determined by the amount of time it takes the ultrasound wave to travel to a partic-ular fixed position and return Thus, the velocity ata series of points across the diameter of a blood vessel ("sample volumes") can be accurately and instantaneously determined.
The positioning of a pulsed-wave doppler trans-ducer in a blood vessel is critical since the distribu-tion of velocity across a vessel ("velocity profile") may not be uniform and a fixed reference is needed in order to measure these different^velocities across the diameter of the entire blood vessel. The positioning of the catheter at the center of a blood vessel, as for electromagnetic transducers, is suboptimal ~ecause the doppler transducer measures velocity in a linear distri-bution resulting in the measurement of only the maximum .. ~ _~ . .
velocity at the center of the blood vessel or some por-tion of the entire velocity profile. In order ~o deter-mine the true volumetric rate of flow, the average velo-city (obtained from the entire velocity profile3 and vessel cross-sectional area (obtained from the vessel diameter) must be known. Both the velocity profile and diameter may be determined using a pulsed wave doppler transducer, if the transducer is placed along one vessel wall and the transmitted ultrasound signal is directed through the blood vessel diameter. One method of accom-plishing this is through the use of an external collar containing the doppler transducer which is surgically implanted around the blood vessel. Such a collar is described in a Ph.D. dissertation by James Knutti of Stanford University entitled "Totally Implantable Bidi-rectional Pulsed Doppler Blood Flow Telemetry: Integrated Ultrasonic Receiver, Diameter Detection, and Volume Flow Estimation" (July, 1977).
X~'' 1 In view of the limitati~ns of known catheters, a need exists for an improved catheter having a position-ing device for positioning the catheter intravenously against one of the walls of the blood vessel in which blood flow velocity is to be measured.
The present invention is directed to a cathe-ter having a mechanism for positioning a doppler shift transducer carried by the catheter against a side wall of a blood vessel. A portion of the catheter near the distal end is adjustable for movement between a first position in line with the axis of th~ catheter and a second position in which such cat~eter portion is in the shape of an arc extending outward from the axis of the catheter such that the arcuate portion will wedge the body of the catheter against the opposite wall of the blood vessel. The adjustable portion can be mani-pulated using a mechanism near the proximal end of the catheter outside of a patient's body.
In one embodiment of the invention, the adjust-able portion of the catheter is a pliable filament or wire which extends through the catheter and is exposed by a slot in the catheter near the distal end. After the catheter is inserted into the blood vessel, this wire is forced inwardly by a screw adjuster at the prox-imal end, causing the portion within the slot to bend : and extend outwardly from the catheter body, thereby forming an arc. When the wire contacts one wall of the blood vessel, it thus forces the body of the catheter against the opposite wall of the blood vessel, thereby positioning the doppler shift transducer against such other wall of the blood vessel and aiming the ultra-sound beam from such transducer through the center of the blood vessel diameter.
In another embodiment of the invention, the portion of the catheter near the distal end is preformed ~2~
. . ~ / , to define an arcuate shape, such as an "S" or a loop shape. A stiffening filament or wire inserted through a lumen in the catheter keeps the catheter straight while it is inserted into a blood vessel. After the catheter is in place, the stiffening wire is removed, allowing the catheter to assume its preformed shape, thus causing the catheter to be wedged against a side wall of the blood vessel. The transducer can either be placed on the body of the catheter at its tip or at the apex of the portion which is preformed in an arc.
In another embodiment of the invention, the transducer and arcuate portion of the catheter are located at a distance from the distal end of the catheter. The catheter can then be inserted through a vein, advanced through the right side of the heart and into the pulmonary artery in a manner similar to that previously described.
A balloon between the distal end and the doppler shift ~ransducer can then be lnflated so that a pressure sensor on the distal tip of the catheter can sense pressures on the left side of the heart while the doppler shift transducer ~onitors blood flow on the right ~id~ of the heart.
For a fuller understanding of the nature and advantages of the invention, reference should be made to the ensuing detailed description taXen in con~unction with the accomp~nying drawings.
Fig. 1 is a side elevational view of the distal extremity of a preferr~d embodiment of the catheter of the present invention in place of a blood vessel and showing a flexible elongate element forming a part of the catheter extended and engaging the vessel wall;
Fig. 2A is an enlarged and side elevational view of the preferred embodiment of the catheter showing the flexible elongate element retracted;
Figure 2B is a top plan view of the distal extremity of the catheter shown in Fig. l;
,~ ~L.25~ tl Fig. 2C is a cros~ ~ectional view taken alony the line 2C-2C of Flg. 2A.
Fig. 3 is a ~ide elevational view, similar to Fig.
2A, of another embodime~t of the catheter of the present invention ~or the measurement of prsssures on the left side of the heart:
Fig . 3A is a cross ~;ectional view taken along line 3A-3A of Fi~. 3.
Fig. 4 is a side elevational view, of another embodiment of the present invention using a preformed "S"-shaped catheter body; and Fig. 5 is a ~ide elevational view of a fourth embodiment of the present invention using a preformed loop-shaped catheter body.
Figs. 2A and 2B how side and top views, respectively, of a catheter 10. Catheter 10 has a wire 14 which is exposed by a slot 16 near the distal end of the catheter. A transducer 20 is mounted at the distal end of catheter 10 and has a face 21 which is oriented so that a line perpendicular to the face defines an angle 0 with the axis of catheter 10. Transducer 20 is covered by an epoxy or other coating 26. Catheter 10 has three lumens 2B, 30, and 32. Wire 13 extends through lumen 28 to a proximal end 34 of catheter 10. Lu~en 28 i6 coupled to an output tube 36 having a pair of ports 38 and 40. Proximal end of wire 14 extends through a channeled fitting of port 40. A
nut 42 of port 40 can be rotated, thereby threading wire 14 into port 40 and moving wire 14 to the position shown in Fig. 1. Port 38 is coupled to a device outside the patient for mesuring the pressure of the blood as sensed through slot 16. A pair of wires 44 at the distal end of catheter 10 are attached to transducer 20 and extend through the catheter, through lumen 32 and through proximal end 34. These wires 44 can be coupled to appropriate instrumentation for controlling doppler transducer 20. A port 46 is coupled to a lumen 30 which i6 connected to a hole 48 beneath latex balloon 22.
Balloon 22 can be inflated by pumping air through port 46 along lumen 30 and out hole 48 to fill the balloon.
t ~
~2595~
~ig. 1 shows a preferred embodiment of the catheter of the present invention in place in an artery.
Catheter 10 is shown as being wedged against a side wall portion 12 of an artery. Wire 14 extends from slot 16 in catheter 10. Wire 14 engages and is wedged against a second side wall portion 18 of the artery. Doppler shift transducer 20 is located at the distal end of the catheter. Immediately behind transducer 2D is balloon 22 which can be inflated as needed. ~ series of points 24 indicate various positions ("sample volumes") within the artery at which the velocity of the blood will be measured by the catheter.
In operation, a series of short bursts of ultrasound waves or signals are emitted by transducer 20 along a line passing through points 24 along the vessel diameter. Points 24 are along a line which de-fines an angle ~ relative to the axis of catheter 10 and the artery wall. The reflected waves or signals are sampled at a series of intervals corresponding to ~0 the round-trip transit times between transducer 20 and the positions 24. The blood flow velocity for each point 24 can then be determined by detecting the doppler frequency shift of the transmitted signal using known techniques. In addition, the direction of the blood flow can be determined by using two reference ultrasonic signals that are generated 90 out of ph~se with each other. The direction of the blood flow can then be determined from the phase shift of the reflected doppler signal as compared to the two reference signals in a conventional manner.
If the blood vessel is assumed to be circular in diameter, the velocity of the blood at each samp'e point 24 can be assumed to be the velocity at all points at an equal radius from the central axis of the blood vessel. To determine the flow volume per unit time of the blood vessel, the cross sectional area of the blood vessel and the average velocity across the blood vessel 351t1 cross-secl--ion at ~ny installt of time (the "space average velocity") can be calculated with the multiple of such area and velocity being the flow volume per unit time.
The flow volume per unit time is thus given by:
Q = VA
where v = the space average velocity, A = the cross sectional area in the plane perpendicular to the velocity vector, and Q = the volumetric flow per unit time.
ThP space average velocity can be determined if the velocities calculated from the doppler shift frequency : at a number of points 24 across the blood vessel are known. Each velocity point is weighted according to the corresponding area of concentric regions within the vessel.
The space average velocity is given by the following equation:
V = 1 ~ { [V(ri) + V(r_i)] (2i-1)~
2NZ i=l where: ri = distance from center of blood vessel to concentric region at sample volume (point 24) position = i;
N = total number of points 24 measured;
and : v(ri) = velocity measured at sample volume i at each of points 24 using the doppler shift frequency of the ultrasound beam emitted from transducer 20 at an angle to the main body axis of catheter 10.
- The cross-sectional area of the artery can be determined from its diameter. The diameter can be deter-mined with doppler transducer 20 by determining the point at which the blood flow velocity drops to zero in the artery. This point will be near the far wall 18 of the artery. This determination can be done continuously :~5~35 ~
since the ar-tery diameter and thus cross sectional area can vary as blood is pumped through it in bursts.
This cross-sectional area is given by the following eq~lation:
A(t) - ~d(tl~
where: A(t) = cross-sectional area as function of time; and d(t) = diameter of blood vessel as function of time.
At any given instant of time, the following equation is true:
tr d 2csin~
where: d = true diameter of the blood vessel in a plane perpendicular to the axial velocity vector;
tr = transmit time for ultrasonic burst to traverse the blood vessel from transducer 20 to the opposite wall and return to transducer 20;
c = velocity of the ultrasound beam; and = angle between the ultrasound beam and the vessel wall, or between a line perpendicular to face 21 of transducer 20 and the main body axis of catheter lO.
A feedback loop in the controlling circuitry (not shown) outside the patient's body can be used to adjust the positions of points 24 so that one point will always he positioned at far wall 18.
Catheter 10 of Fig. 1 preferably has a diame-ter of 2mm and is made of a suitable flexible material, such as polyethylene. Catheter 10 may be inserted via the internal jugular vein or femoral vein and the latex balloon 22 can then be inflated with air. The balloon will extend across the flow of blood and will be advanced 5~35 ~i by t:he hlood fLow, ~)uJIillg the catheter ~0 along with it. The catheter may be advanced in-to the right atrium, through the tricuspid valve, the right ventricle, and the p~ onary valve with -the doppler transducer 20 even-tually being placed in -the main pulmonary artery. The positioning of the catheter in the pulmonary artery may be confirmed either fluoroscopically or or by monitoring the pressure waveform transduced from slot 16 through lumen 28 connected to port 38 and coupled to a dynamic pressure sensing device (not shown).
A 6MHz doppler crystal may, for example, be used as transducer 20. The crystal should be capable of determining velocity at eight to ten points 24 lo-cated at predetermined distances from the transducer 20. In operation, the returning doppler-shifted fre-quency signals are quadrature phase detected and compared to the original signal to determine the velocity and the direction of flow at a particular position 24. A
real time two-dimensional velocity profile combining the eight to ten positions 24 may then be constructed ~ using either a zero crossing counter or spectral analy-sis of the quadrature audio output of the transducer 20. The angle of incidence between the doppler ultra-sound beam and the velocity vector of the blood, ~, is known from the design of the catheter 10 because a line perpendicular to face 21 of transducer 20 is at a known angle, ~, to the main body axis of catheter 10, which - will be parallel to the velocity vector.
Fig. 3 shows another embodiment of the ca~he-ter of the present invention. A doppler transducer 50is located at a point spaced from the distal end of the catheter. A wire guide 54 in a slot 56 is located imme-diately behind doppler transducer 50. The proximal end of wire guide 54 extends through a channeled fitting of port 78. A nut 79 of port 78 can be rotated, thereby thread-ing wire 54 into port 78 and moving the wire into an arc-uate position. An opening 66 at the distal end of the _ . .
~ 2~
l2 catheter provides ~ pressure measuring outlet. Immedi-ately behind opening 66 is a balloon 68. A pair of wires 58 at the dist~l end at the catheter are attached to transducer crystal 50 and extend through the catheter throuyh one of the lumens.
The proximal end 70 of the catheter has a number of ports, including two pressure ports 72 and 74. Pressure port 72 is coupled to output tube 73 which is coupled to port 78 and through one of four lumens to slot 56 to provide a pressure reading. Port 74 is cou-pled through another lumen to hole 66 to provide a dis-tal pressure reading. ~alloon 68 can be inflated, there-by blocking pressures from the right side of the heart and exposing hole 66 to pulmonary venous pressures which in turn reflect pressures on the left side of the heart while slot 56 will give pressure readings from the pul-monary artery and right side of the heart. The other ports are a balloon inflation port 76 and a port having guide wire adjustment screw 78.
In operation, the catheter of Fig. 3 may be advanced in a manner similar to a standard balloon wedge pressure catheter into the proximal pulmonary artery, through one of the main pulmonary artery branches, and ~- into a distal pulmonary artery segment to the point at which the balloon becomes wedged in the artery. Distal hole 66 is now in communication with the pulmonary veins and may be used to measure pulmonary venous pressures.
The proximal doppler crystal 50 may meanwhile be placed against the wall of the main pulmonary artery by advanc-ing wire 54 into its arcuate position, wedged against a side wall portion of the artery in a manner similar to that described with reference to Fig. 1 above. Its ~ position can be confirmed by monitoring the transduced pressure wave of the proximal pressure from slot 56 as observed at port 72. A velocity profile through thecenter of the pulmonary artery can then be obtained in the manner similar to that described with reference to .. . ... . .. -- -- --
bl c~llC}l whi(.-h i~. in di ?:~t communication with the pulmo-nary veins and which, in turn, reflect pressures on the left side of the heart.
Methods for measuring mean volumetric blood flow in man include thexmal dilution, dye dilution, and "Fick" oxygcn consumption methods. More recent devices have been developed to measure the instantaneous flow of blood in a vessel or artery. These include methods used to measure instantaneous flow by measuring changes in a concentric magnetic field across the blood vessel.
To generate the concentric magnetic field requires either a cuff surgically placed around the vessel or a catheter precisely centered in the middle of the blood vessel.
One method for centering an electromagnetic-type catheter is -to use an umbrella-like spring having a number of "V"-shaped spring elements with one end of the "V" coupled to the catheter and the other end coupled to a movable collar on the catheter. By moving the collar outwardly, the springs are made to expand and 20~ extend outward away from the catheter until the blood vessel walls are contacted. By using a number of these springs around the catheter, the catheter tip will be centered in the middle of the blood vessel. Such a centering device is disclosed in an article entitled "Registration of Phasic Changes of Bloodflow by Means of a Catheter-type Flow Meter," H. Piper, The Review of Scientific Instruments, Vol. 29, No. 11, p. 965 (Novem-ber, 1958).
Techniques for measuring volumetric blood flow require the determination of the diameter of the blood vessel in order to determine the total volume of blood flow through the vessel itself. One method of determining the diameter is similar to the above-de-scribed centering device. A number of hinged braces near the end of a catheter tip are extended outwardly when a cuff to which they are attached slides along the catheter length. When these braces contact the blood ~5~
vesscl wal~s, a signal proportional to the diameter of the blood vessel is produced and sensed. Such a mecha-nism is disclosed in an article entitled "Catheter-Tip Gauge for Measllring Blood Flow Velocity and Vessel Di-ameter in Dogs," Piper and Paul, Journal of Applied Physiology, Vol. 24, No. 2, p. 259 ~February, 196~).
Positioning problems may arise when a flow transducer is desired to be placed at the entrance to a small blood vessel branching off of a larger blood ves-sel. One method for accomplishing this involves attach-ing a wire to the end of the catheter similar to the bow string of a bow and arrow set. The transducer is placed at the center of that portion of the catheter directly opposite the wire that will be bowed. The catheter is then inserted into the main blood vessel until the transducer is adjacent to the entrance of the smaller blood vessel. The wire can then be pulled, thereby bowing the catheter and forcing the transducer against the entrance to the smaller blood vessel. See 20~ "An Electromagnetic ~atheter-Flow Meter," Kolin and Archer, Circulation Research, p. 889 (December, 1967).
A doppler ultrasonic technique for measuring blood flow velocity uses a transmitter to transmit ul-trasound across a blood vessel and a receiver to detect the change in frequency and phase shift of the reflected ultrasound signals. The measured frequency change is due to the movement of the blood cells which reflect the signals ("Doppler effect").
In one type of doppler flow meter ("continuous wave"), two transducers are used. One transducer con-tinuously transmits ultrasound signals and the other continuously receives the reflected ultrasound signals.
A weighting technique can then be used with readings from this type of doppler flow meter to determine the average velocity.
A pulsed-wave doppler technique uses a single crystal transducer with the received signal being sampled - ~25~
at c~rtain s,pccified intervals. These intervals corre-spond to different fixed posi-tions across the blood vessel. The intervals are determined by the amount of time it takes the ultrasound wave to travel to a partic-ular fixed position and return Thus, the velocity ata series of points across the diameter of a blood vessel ("sample volumes") can be accurately and instantaneously determined.
The positioning of a pulsed-wave doppler trans-ducer in a blood vessel is critical since the distribu-tion of velocity across a vessel ("velocity profile") may not be uniform and a fixed reference is needed in order to measure these different^velocities across the diameter of the entire blood vessel. The positioning of the catheter at the center of a blood vessel, as for electromagnetic transducers, is suboptimal ~ecause the doppler transducer measures velocity in a linear distri-bution resulting in the measurement of only the maximum .. ~ _~ . .
velocity at the center of the blood vessel or some por-tion of the entire velocity profile. In order ~o deter-mine the true volumetric rate of flow, the average velo-city (obtained from the entire velocity profile3 and vessel cross-sectional area (obtained from the vessel diameter) must be known. Both the velocity profile and diameter may be determined using a pulsed wave doppler transducer, if the transducer is placed along one vessel wall and the transmitted ultrasound signal is directed through the blood vessel diameter. One method of accom-plishing this is through the use of an external collar containing the doppler transducer which is surgically implanted around the blood vessel. Such a collar is described in a Ph.D. dissertation by James Knutti of Stanford University entitled "Totally Implantable Bidi-rectional Pulsed Doppler Blood Flow Telemetry: Integrated Ultrasonic Receiver, Diameter Detection, and Volume Flow Estimation" (July, 1977).
X~'' 1 In view of the limitati~ns of known catheters, a need exists for an improved catheter having a position-ing device for positioning the catheter intravenously against one of the walls of the blood vessel in which blood flow velocity is to be measured.
The present invention is directed to a cathe-ter having a mechanism for positioning a doppler shift transducer carried by the catheter against a side wall of a blood vessel. A portion of the catheter near the distal end is adjustable for movement between a first position in line with the axis of th~ catheter and a second position in which such cat~eter portion is in the shape of an arc extending outward from the axis of the catheter such that the arcuate portion will wedge the body of the catheter against the opposite wall of the blood vessel. The adjustable portion can be mani-pulated using a mechanism near the proximal end of the catheter outside of a patient's body.
In one embodiment of the invention, the adjust-able portion of the catheter is a pliable filament or wire which extends through the catheter and is exposed by a slot in the catheter near the distal end. After the catheter is inserted into the blood vessel, this wire is forced inwardly by a screw adjuster at the prox-imal end, causing the portion within the slot to bend : and extend outwardly from the catheter body, thereby forming an arc. When the wire contacts one wall of the blood vessel, it thus forces the body of the catheter against the opposite wall of the blood vessel, thereby positioning the doppler shift transducer against such other wall of the blood vessel and aiming the ultra-sound beam from such transducer through the center of the blood vessel diameter.
In another embodiment of the invention, the portion of the catheter near the distal end is preformed ~2~
. . ~ / , to define an arcuate shape, such as an "S" or a loop shape. A stiffening filament or wire inserted through a lumen in the catheter keeps the catheter straight while it is inserted into a blood vessel. After the catheter is in place, the stiffening wire is removed, allowing the catheter to assume its preformed shape, thus causing the catheter to be wedged against a side wall of the blood vessel. The transducer can either be placed on the body of the catheter at its tip or at the apex of the portion which is preformed in an arc.
In another embodiment of the invention, the transducer and arcuate portion of the catheter are located at a distance from the distal end of the catheter. The catheter can then be inserted through a vein, advanced through the right side of the heart and into the pulmonary artery in a manner similar to that previously described.
A balloon between the distal end and the doppler shift ~ransducer can then be lnflated so that a pressure sensor on the distal tip of the catheter can sense pressures on the left side of the heart while the doppler shift transducer ~onitors blood flow on the right ~id~ of the heart.
For a fuller understanding of the nature and advantages of the invention, reference should be made to the ensuing detailed description taXen in con~unction with the accomp~nying drawings.
Fig. 1 is a side elevational view of the distal extremity of a preferr~d embodiment of the catheter of the present invention in place of a blood vessel and showing a flexible elongate element forming a part of the catheter extended and engaging the vessel wall;
Fig. 2A is an enlarged and side elevational view of the preferred embodiment of the catheter showing the flexible elongate element retracted;
Figure 2B is a top plan view of the distal extremity of the catheter shown in Fig. l;
,~ ~L.25~ tl Fig. 2C is a cros~ ~ectional view taken alony the line 2C-2C of Flg. 2A.
Fig. 3 is a ~ide elevational view, similar to Fig.
2A, of another embodime~t of the catheter of the present invention ~or the measurement of prsssures on the left side of the heart:
Fig . 3A is a cross ~;ectional view taken along line 3A-3A of Fi~. 3.
Fig. 4 is a side elevational view, of another embodiment of the present invention using a preformed "S"-shaped catheter body; and Fig. 5 is a ~ide elevational view of a fourth embodiment of the present invention using a preformed loop-shaped catheter body.
Figs. 2A and 2B how side and top views, respectively, of a catheter 10. Catheter 10 has a wire 14 which is exposed by a slot 16 near the distal end of the catheter. A transducer 20 is mounted at the distal end of catheter 10 and has a face 21 which is oriented so that a line perpendicular to the face defines an angle 0 with the axis of catheter 10. Transducer 20 is covered by an epoxy or other coating 26. Catheter 10 has three lumens 2B, 30, and 32. Wire 13 extends through lumen 28 to a proximal end 34 of catheter 10. Lu~en 28 i6 coupled to an output tube 36 having a pair of ports 38 and 40. Proximal end of wire 14 extends through a channeled fitting of port 40. A
nut 42 of port 40 can be rotated, thereby threading wire 14 into port 40 and moving wire 14 to the position shown in Fig. 1. Port 38 is coupled to a device outside the patient for mesuring the pressure of the blood as sensed through slot 16. A pair of wires 44 at the distal end of catheter 10 are attached to transducer 20 and extend through the catheter, through lumen 32 and through proximal end 34. These wires 44 can be coupled to appropriate instrumentation for controlling doppler transducer 20. A port 46 is coupled to a lumen 30 which i6 connected to a hole 48 beneath latex balloon 22.
Balloon 22 can be inflated by pumping air through port 46 along lumen 30 and out hole 48 to fill the balloon.
t ~
~2595~
~ig. 1 shows a preferred embodiment of the catheter of the present invention in place in an artery.
Catheter 10 is shown as being wedged against a side wall portion 12 of an artery. Wire 14 extends from slot 16 in catheter 10. Wire 14 engages and is wedged against a second side wall portion 18 of the artery. Doppler shift transducer 20 is located at the distal end of the catheter. Immediately behind transducer 2D is balloon 22 which can be inflated as needed. ~ series of points 24 indicate various positions ("sample volumes") within the artery at which the velocity of the blood will be measured by the catheter.
In operation, a series of short bursts of ultrasound waves or signals are emitted by transducer 20 along a line passing through points 24 along the vessel diameter. Points 24 are along a line which de-fines an angle ~ relative to the axis of catheter 10 and the artery wall. The reflected waves or signals are sampled at a series of intervals corresponding to ~0 the round-trip transit times between transducer 20 and the positions 24. The blood flow velocity for each point 24 can then be determined by detecting the doppler frequency shift of the transmitted signal using known techniques. In addition, the direction of the blood flow can be determined by using two reference ultrasonic signals that are generated 90 out of ph~se with each other. The direction of the blood flow can then be determined from the phase shift of the reflected doppler signal as compared to the two reference signals in a conventional manner.
If the blood vessel is assumed to be circular in diameter, the velocity of the blood at each samp'e point 24 can be assumed to be the velocity at all points at an equal radius from the central axis of the blood vessel. To determine the flow volume per unit time of the blood vessel, the cross sectional area of the blood vessel and the average velocity across the blood vessel 351t1 cross-secl--ion at ~ny installt of time (the "space average velocity") can be calculated with the multiple of such area and velocity being the flow volume per unit time.
The flow volume per unit time is thus given by:
Q = VA
where v = the space average velocity, A = the cross sectional area in the plane perpendicular to the velocity vector, and Q = the volumetric flow per unit time.
ThP space average velocity can be determined if the velocities calculated from the doppler shift frequency : at a number of points 24 across the blood vessel are known. Each velocity point is weighted according to the corresponding area of concentric regions within the vessel.
The space average velocity is given by the following equation:
V = 1 ~ { [V(ri) + V(r_i)] (2i-1)~
2NZ i=l where: ri = distance from center of blood vessel to concentric region at sample volume (point 24) position = i;
N = total number of points 24 measured;
and : v(ri) = velocity measured at sample volume i at each of points 24 using the doppler shift frequency of the ultrasound beam emitted from transducer 20 at an angle to the main body axis of catheter 10.
- The cross-sectional area of the artery can be determined from its diameter. The diameter can be deter-mined with doppler transducer 20 by determining the point at which the blood flow velocity drops to zero in the artery. This point will be near the far wall 18 of the artery. This determination can be done continuously :~5~35 ~
since the ar-tery diameter and thus cross sectional area can vary as blood is pumped through it in bursts.
This cross-sectional area is given by the following eq~lation:
A(t) - ~d(tl~
where: A(t) = cross-sectional area as function of time; and d(t) = diameter of blood vessel as function of time.
At any given instant of time, the following equation is true:
tr d 2csin~
where: d = true diameter of the blood vessel in a plane perpendicular to the axial velocity vector;
tr = transmit time for ultrasonic burst to traverse the blood vessel from transducer 20 to the opposite wall and return to transducer 20;
c = velocity of the ultrasound beam; and = angle between the ultrasound beam and the vessel wall, or between a line perpendicular to face 21 of transducer 20 and the main body axis of catheter lO.
A feedback loop in the controlling circuitry (not shown) outside the patient's body can be used to adjust the positions of points 24 so that one point will always he positioned at far wall 18.
Catheter 10 of Fig. 1 preferably has a diame-ter of 2mm and is made of a suitable flexible material, such as polyethylene. Catheter 10 may be inserted via the internal jugular vein or femoral vein and the latex balloon 22 can then be inflated with air. The balloon will extend across the flow of blood and will be advanced 5~35 ~i by t:he hlood fLow, ~)uJIillg the catheter ~0 along with it. The catheter may be advanced in-to the right atrium, through the tricuspid valve, the right ventricle, and the p~ onary valve with -the doppler transducer 20 even-tually being placed in -the main pulmonary artery. The positioning of the catheter in the pulmonary artery may be confirmed either fluoroscopically or or by monitoring the pressure waveform transduced from slot 16 through lumen 28 connected to port 38 and coupled to a dynamic pressure sensing device (not shown).
A 6MHz doppler crystal may, for example, be used as transducer 20. The crystal should be capable of determining velocity at eight to ten points 24 lo-cated at predetermined distances from the transducer 20. In operation, the returning doppler-shifted fre-quency signals are quadrature phase detected and compared to the original signal to determine the velocity and the direction of flow at a particular position 24. A
real time two-dimensional velocity profile combining the eight to ten positions 24 may then be constructed ~ using either a zero crossing counter or spectral analy-sis of the quadrature audio output of the transducer 20. The angle of incidence between the doppler ultra-sound beam and the velocity vector of the blood, ~, is known from the design of the catheter 10 because a line perpendicular to face 21 of transducer 20 is at a known angle, ~, to the main body axis of catheter 10, which - will be parallel to the velocity vector.
Fig. 3 shows another embodiment of the ca~he-ter of the present invention. A doppler transducer 50is located at a point spaced from the distal end of the catheter. A wire guide 54 in a slot 56 is located imme-diately behind doppler transducer 50. The proximal end of wire guide 54 extends through a channeled fitting of port 78. A nut 79 of port 78 can be rotated, thereby thread-ing wire 54 into port 78 and moving the wire into an arc-uate position. An opening 66 at the distal end of the _ . .
~ 2~
l2 catheter provides ~ pressure measuring outlet. Immedi-ately behind opening 66 is a balloon 68. A pair of wires 58 at the dist~l end at the catheter are attached to transducer crystal 50 and extend through the catheter throuyh one of the lumens.
The proximal end 70 of the catheter has a number of ports, including two pressure ports 72 and 74. Pressure port 72 is coupled to output tube 73 which is coupled to port 78 and through one of four lumens to slot 56 to provide a pressure reading. Port 74 is cou-pled through another lumen to hole 66 to provide a dis-tal pressure reading. ~alloon 68 can be inflated, there-by blocking pressures from the right side of the heart and exposing hole 66 to pulmonary venous pressures which in turn reflect pressures on the left side of the heart while slot 56 will give pressure readings from the pul-monary artery and right side of the heart. The other ports are a balloon inflation port 76 and a port having guide wire adjustment screw 78.
In operation, the catheter of Fig. 3 may be advanced in a manner similar to a standard balloon wedge pressure catheter into the proximal pulmonary artery, through one of the main pulmonary artery branches, and ~- into a distal pulmonary artery segment to the point at which the balloon becomes wedged in the artery. Distal hole 66 is now in communication with the pulmonary veins and may be used to measure pulmonary venous pressures.
The proximal doppler crystal 50 may meanwhile be placed against the wall of the main pulmonary artery by advanc-ing wire 54 into its arcuate position, wedged against a side wall portion of the artery in a manner similar to that described with reference to Fig. 1 above. Its ~ position can be confirmed by monitoring the transduced pressure wave of the proximal pressure from slot 56 as observed at port 72. A velocity profile through thecenter of the pulmonary artery can then be obtained in the manner similar to that described with reference to .. . ... . .. -- -- --
3~ tl.
Fig. 1 above. Tl~e advan~age of this design is its abil-ity to monitor both the instantaneous cardiac output alonq with pulmonary artery and pulmonary venous pres-sures.
Fig. 4 shows another embodiment of the pre-sent invention. The catheter of -this embodiment is preformed into an S-shaped curve as indicated in the figure. A doppler crystal transducer 80 is located on the underside of the curve at approximately the apex thereof. A guide wire can be inserted through one of the four lumens to initially straighten the catheter for insertion into the venous system. The guide wire must be of sufficient strength to straighten the cathe-ter and of sufficient flexibility to allow for ease of insertion of the catheter. The catheter is advanced as -- described above with respect to Fig. 3. Once in place, the guide wire is removed, allowing the catheter to assume its preformed shape. In this prefor~ed shape, the portion of the catheter proximate transducer 80 will be wedged against a side wall of the artery. This catheter has a distal pressure hole 82 and a proximal pressure hole 84, as indicated. A balloon 86 is inflated to separate the two pressure holes 82, 84, as described with reference to Fig. 3, above.
Another embodiment of the present invention is shown in Fig. 5. In this embodiment the catheter is preformed into a spiral loop shape, as shown. Doppler crystal 88 is l-ocated at the apex of the loop. When in place in an artery, transducer 88 will be at the portion of the catheter wedged against a side wall of the artery.
Because the loop is in a spiral, the portion of the loop opposite transducer 88 will not be in line with - the transducer and thus will not interfere with the velocity measurements. This embodiment also contains distal pressure hole 90 and proximal pressure hole 92 along with a balloon 94. The operation of the catheter of Fig. 5 is similar to that for Fig. 4, above, using ~.~ ~ 59 1~
arl inteln(~ e wire t:o stl:aig~lten the catheter on insertion with the guide wire being removed when the catheter is desired to be fixed in place.
The catheter of the present invention allows one to simultaneously measure instantaneous volumetric flow, blood vessel diameter, instantaneous velocity profile, and pulmonary artery pressure and/or pulmonary venous pressure. This combination of hemodynamic para-meters will allow a physician to obtain a more accurate assessment of the patient's cardiovascular state at any time and the changes in such state with various physio-logical and pharmacological interventions. Mapping of the velocity profile of the major blood vessels may also provide the physician with a better understanding of the basic disease processes of these vessels and the heart in general.
As will be understood by those familiar with the art, the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. For example, other shapes than those disclosed in Figs. 4 and S could be used, or a three-lumen catheter could be used in place of the four-lumen catheter by removing one of the func-tions, or more lumens could be added. Alternative means of calculating volumetric flow utilizing information concerning doppler frequency shift and vessel diameter, obtained from the doppler transducer, could also be employed. Accordingly, the disclosure of the preferred.
embodiments of the present invention is intended to be illustrative, but not limiting, of the scope of the invention which is set forth in the following claims.
Fig. 1 above. Tl~e advan~age of this design is its abil-ity to monitor both the instantaneous cardiac output alonq with pulmonary artery and pulmonary venous pres-sures.
Fig. 4 shows another embodiment of the pre-sent invention. The catheter of -this embodiment is preformed into an S-shaped curve as indicated in the figure. A doppler crystal transducer 80 is located on the underside of the curve at approximately the apex thereof. A guide wire can be inserted through one of the four lumens to initially straighten the catheter for insertion into the venous system. The guide wire must be of sufficient strength to straighten the cathe-ter and of sufficient flexibility to allow for ease of insertion of the catheter. The catheter is advanced as -- described above with respect to Fig. 3. Once in place, the guide wire is removed, allowing the catheter to assume its preformed shape. In this prefor~ed shape, the portion of the catheter proximate transducer 80 will be wedged against a side wall of the artery. This catheter has a distal pressure hole 82 and a proximal pressure hole 84, as indicated. A balloon 86 is inflated to separate the two pressure holes 82, 84, as described with reference to Fig. 3, above.
Another embodiment of the present invention is shown in Fig. 5. In this embodiment the catheter is preformed into a spiral loop shape, as shown. Doppler crystal 88 is l-ocated at the apex of the loop. When in place in an artery, transducer 88 will be at the portion of the catheter wedged against a side wall of the artery.
Because the loop is in a spiral, the portion of the loop opposite transducer 88 will not be in line with - the transducer and thus will not interfere with the velocity measurements. This embodiment also contains distal pressure hole 90 and proximal pressure hole 92 along with a balloon 94. The operation of the catheter of Fig. 5 is similar to that for Fig. 4, above, using ~.~ ~ 59 1~
arl inteln(~ e wire t:o stl:aig~lten the catheter on insertion with the guide wire being removed when the catheter is desired to be fixed in place.
The catheter of the present invention allows one to simultaneously measure instantaneous volumetric flow, blood vessel diameter, instantaneous velocity profile, and pulmonary artery pressure and/or pulmonary venous pressure. This combination of hemodynamic para-meters will allow a physician to obtain a more accurate assessment of the patient's cardiovascular state at any time and the changes in such state with various physio-logical and pharmacological interventions. Mapping of the velocity profile of the major blood vessels may also provide the physician with a better understanding of the basic disease processes of these vessels and the heart in general.
As will be understood by those familiar with the art, the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. For example, other shapes than those disclosed in Figs. 4 and S could be used, or a three-lumen catheter could be used in place of the four-lumen catheter by removing one of the func-tions, or more lumens could be added. Alternative means of calculating volumetric flow utilizing information concerning doppler frequency shift and vessel diameter, obtained from the doppler transducer, could also be employed. Accordingly, the disclosure of the preferred.
embodiments of the present invention is intended to be illustrative, but not limiting, of the scope of the invention which is set forth in the following claims.
Claims (32)
1. A catheter comprising an elongate body for extending through a blood vessel to a proximal end exterior of a person's body, said elongate body having proximal and distal extremities;
an elongate portion of said body near the distal extremity thereof being movable between a first position substantially parallel to the axis of said body and a second position along an arcuate path having an apex and extending outwardly from said first position;
means carried by said body for causing movement of said elongate portion between said first position and said second position to that in said second position, said elongate portion contacts a side wall of said blood vessel and forces aid body against an opposite side wall of said blood vessel and a transducer carried by said elongate body and positioned proximate a side wall of said blood vessel when said elongate portion is in said second position.
an elongate portion of said body near the distal extremity thereof being movable between a first position substantially parallel to the axis of said body and a second position along an arcuate path having an apex and extending outwardly from said first position;
means carried by said body for causing movement of said elongate portion between said first position and said second position to that in said second position, said elongate portion contacts a side wall of said blood vessel and forces aid body against an opposite side wall of said blood vessel and a transducer carried by said elongate body and positioned proximate a side wall of said blood vessel when said elongate portion is in said second position.
2. The apparatus of Claim 1 wherein said elongate portion includes an axial lot in the elongate body, and a pliable filament carried by the elongate body and being disposed within said body in said first position of said elongate portion and being moveable through said axial slot in said second position of said elongate portion.
3. The apparatus of Claim 2 wherein said slot is located such that said transducer is between said slot and said distal end of said elongate body.
4. The apparatus of Claim 1 wherein said transducer is mounted on the distal end of said elongate body.
5. The apparatus of Claim 1 wherein said transducer is mounted on said elongate body at a position spaced apart from the distal end thereof.
6. The apparatus of Claim 1 further comprising an inflatable balloon near said distal end.
7. The apparatus of Claim 1 wherein said transducer i located on said elongate portion so that said transducer will be positioned near an apex of said arcuate path when said elongate portion is in said second position.
8. The apparatus of Claim 7 wherein said elongate body is preformed to assume said second position and wherein said means for causing movement includes a pliable filament internal to said elongate body, said pliable filament holding said elongate body in said first position when the elongate body is in place in a blood vessel, said elongate body assuming said second position when said pliable filament is removed.
9. The apparatus of Claim 8 wherein said elongate position is "S"-shaped.
10. The apparatus of Claim 9 further comprising a pressure hole located at said distal end of said elongate body.
11. The apparatus of Claim 9 further comprising a second pressure hole proximate to said transducer.
12. The apparatus of Claim 9 further comprising an inflatable balloon near said distal end.
13. The apparatus of Claim 8 wherein said elongate portion comprises a 360° spiral loop.
14. The apparatus of Claim 13 further comprising a pressure hole located at the distal end of said elongate body.
15. the apparatus of Claim 13 further comprising a second pressure hole located proximate to said transducer.
16. The apparatus of Claim 13 further comprising an inflatable balloon near said distal end.
17. A catheter comprising:
an elongate body for extending into a blood vessel, said elongate body having proximal and distal extremities:
a pliable filament disposed within said elongate body, said elongate body having an axially extending slot therein, said pliable filament being adjustable between a first position within said slot and a second position along an arcuate path extending outward from said first position and from said slot, a transducer carried by said elongate body near the distal extremity thereof; and means near said proximal extremity of said elongate body for adjusting said pliable filament between said first position and said second position so that in said second position, said pliable filament contacts a side wall of said blood vessel and forces said elongate body against an opposite side wall of said blood vessel so that said transducer is positioned near a side wall of said blood vessel.
an elongate body for extending into a blood vessel, said elongate body having proximal and distal extremities:
a pliable filament disposed within said elongate body, said elongate body having an axially extending slot therein, said pliable filament being adjustable between a first position within said slot and a second position along an arcuate path extending outward from said first position and from said slot, a transducer carried by said elongate body near the distal extremity thereof; and means near said proximal extremity of said elongate body for adjusting said pliable filament between said first position and said second position so that in said second position, said pliable filament contacts a side wall of said blood vessel and forces said elongate body against an opposite side wall of said blood vessel so that said transducer is positioned near a side wall of said blood vessel.
18. A catheter as in Claim 17 wherein said transducer is coupled to the distal end of said elongate body.
19. A catheter as in Claim 17 wherein said transducer is coupled to said elongate body at a position spaced apart from said distal end thereof.
20. A catheter as in Claim 17 wherein said filament is a wire.
21. A catheter comprising:
an elongate catheter body, for extending through a blood vessel to a proximal end exterior of a person' 5 body:
a transducer coupled to a distal end of said catheter body:
a pliable filament disposed within an axial slot within said catheter body, said slot being located such that said transducer is located between said lot and said distal end, said pliable filament being adjustable between a first position within said slot and a second position along an arcuate path extending outward from said first position:
means near said proximal end of said body, for adjusting said pliable filament between said first position and said second position;
an inflatable balloon coupled to said catheter between said transducer and said distal end;
a pressure hole proximate said distal end;
whereby, in said second position, said pliable filament contacts a side wall of said blood vessel, thereby forcing said catheter body against an opposite side wall of said blood vessel so that said transducer can be positioned near a side wall of said blood vessel, said balloon being inflatable to block said blood vessel so that said pressure hole can monitor a pressure isolated from said transducer.
an elongate catheter body, for extending through a blood vessel to a proximal end exterior of a person' 5 body:
a transducer coupled to a distal end of said catheter body:
a pliable filament disposed within an axial slot within said catheter body, said slot being located such that said transducer is located between said lot and said distal end, said pliable filament being adjustable between a first position within said slot and a second position along an arcuate path extending outward from said first position:
means near said proximal end of said body, for adjusting said pliable filament between said first position and said second position;
an inflatable balloon coupled to said catheter between said transducer and said distal end;
a pressure hole proximate said distal end;
whereby, in said second position, said pliable filament contacts a side wall of said blood vessel, thereby forcing said catheter body against an opposite side wall of said blood vessel so that said transducer can be positioned near a side wall of said blood vessel, said balloon being inflatable to block said blood vessel so that said pressure hole can monitor a pressure isolated from said transducer.
22. A catheter comprising:
an elongate body for extending through a blood vessel from a proximal end exterior of a person's body to a distal end in a blood vessel;
A pliable portion of said body near said distal end, said pliable portion being preformed in a first position along an S-shaped arcuate path extending outward from said elongate body;
a pliable filament internal to said elongate body, said filament holding said pliable portion in a second position substantially parallel to the axis of said elongate body, said pliable portion assuming said first position when said filament is removed;
and a transducer coupled to said pliable portion proximate an apex of said S-shaped arcuate path;
whereby, in said first position, said pliable portion contacts a side wall of said blood vessel, thereby forcing said elongate body against an opposite side wall of said blood vessel so that said transducer can be positioned proximate a side wall of aid blood vessel.
an elongate body for extending through a blood vessel from a proximal end exterior of a person's body to a distal end in a blood vessel;
A pliable portion of said body near said distal end, said pliable portion being preformed in a first position along an S-shaped arcuate path extending outward from said elongate body;
a pliable filament internal to said elongate body, said filament holding said pliable portion in a second position substantially parallel to the axis of said elongate body, said pliable portion assuming said first position when said filament is removed;
and a transducer coupled to said pliable portion proximate an apex of said S-shaped arcuate path;
whereby, in said first position, said pliable portion contacts a side wall of said blood vessel, thereby forcing said elongate body against an opposite side wall of said blood vessel so that said transducer can be positioned proximate a side wall of aid blood vessel.
23. The apparatus of Claim 22 further comprising a pressure hole near said distal end of said elongate body.
24. The apparatus of Claim 23 further comprising an inflatable balloon intermediate said pressure hole and said transducer.
25. A catheter comprising:
an elongate body for extending through a blood vessel from a proximal end exterior of a person's body to a distal end in a blood vessel:
a pliable portion of said body near said distal end, said pliable portion being preformed in a first position along a 360° spiral loop arcuate path extending outward from said elongate body;
a pliable filament internal to said elongate body, said filament holding said pliable portion in a second position substantially parallel to the axis of said elongate body, said pliable portion assuming said first position when said filament is removed;
and transducer coupled to said pliable portion proximate an apex of said 350° spiral loop arcuate path;
whereby, in said first position, said pliable portion contacts a side wall of said blood vessel, thereby forcing said elongate body against an opposite side wall of said blood vessel so that said doppler shift transducer can be positioned proximate a side wall of said blood vessel.
an elongate body for extending through a blood vessel from a proximal end exterior of a person's body to a distal end in a blood vessel:
a pliable portion of said body near said distal end, said pliable portion being preformed in a first position along a 360° spiral loop arcuate path extending outward from said elongate body;
a pliable filament internal to said elongate body, said filament holding said pliable portion in a second position substantially parallel to the axis of said elongate body, said pliable portion assuming said first position when said filament is removed;
and transducer coupled to said pliable portion proximate an apex of said 350° spiral loop arcuate path;
whereby, in said first position, said pliable portion contacts a side wall of said blood vessel, thereby forcing said elongate body against an opposite side wall of said blood vessel so that said doppler shift transducer can be positioned proximate a side wall of said blood vessel.
26. The apparatus of Claim 25 further comprising a pressure hole near said distal end of said elongate body.
27. The apparatus of Claim 26 further comprising an inflatable balloon intermediate said pressure hole and said transducer.
28. In a device for making measurements in a blood vessel, a flexible elongate element adapted to be inserted into the blood vessel and having a plurality of lumens extending longitudinally thereof, said elongate element having proximal and distal ends, a transducer carried by the elongate element and means carried by the elongate element for causing a portion of the elongate element to be urged against the wall of the blood vessel 60 that it remains in a relatively fixed position during pulsatile flow of blood through the blood vessel; said transducer being disposed in relatively close proximity to said portion whereby said portion provides a desired orientation for the transducer.
29. A device as in Claim 28 together with inflatable balloon means carried by the elongate element near the distal extremity thereof and having the interior thereof in communication with one of said lumens.
30. A device as in Claim 29 wherein the means carried by the element for causing said portion of said elongate element to be urged against the wall of the blood vessel includes a flexible member extending through at least a portion of another of said lumens.
31. A device as in Claim 30 wherein said elongate element is formed with a slot therein extending longitudinally thereof and wherein a portion of said flexible member extends through said slot causing said portion to be urged against the wall of the vessel.
32. A device as in Claim 28 wherein said transducer is an ultrasonic transducer and wherein said orientation of said transducer is such that the ultrasonic energy emanating from said transducer passes through a central longitudinal axis of the blood vessel.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US06/737,650 US4733669A (en) | 1985-05-24 | 1985-05-24 | Blood flow measurement catheter |
| US737,650 | 1985-05-24 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1259541A true CA1259541A (en) | 1989-09-19 |
Family
ID=24964730
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000509795A Expired CA1259541A (en) | 1985-05-24 | 1986-05-23 | Blood flow measurement catheter |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US4733669A (en) |
| JP (1) | JPS6211466A (en) |
| CA (1) | CA1259541A (en) |
| DE (1) | DE3615341A1 (en) |
| FR (1) | FR2582213B1 (en) |
Families Citing this family (123)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4671295A (en) * | 1985-01-15 | 1987-06-09 | Applied Biometrics, Inc. | Method for measuring cardiac output |
| US4889128A (en) * | 1985-09-13 | 1989-12-26 | Pfizer Hospital Products | Doppler catheter |
| US5000185A (en) * | 1986-02-28 | 1991-03-19 | Cardiovascular Imaging Systems, Inc. | Method for intravascular two-dimensional ultrasonography and recanalization |
| EP0286359A3 (en) * | 1987-04-10 | 1991-12-11 | Cardiometrics, Inc. | Apparatus, system and method for measuring volumetric flow of blood in a vessel |
| US5105818A (en) * | 1987-04-10 | 1992-04-21 | Cardiometric, Inc. | Apparatus, system and method for measuring spatial average velocity and/or volumetric flow of blood in a vessel and screw joint for use therewith |
| NL8701536A (en) * | 1987-06-30 | 1989-01-16 | Joannes Hendricus Aloys Heuvel | METHOD FOR PERFORMING HAEMODYNAMIC MEASUREMENTS IN A PATIENT AND FLOW-GUIDED BALLOON CATHETER USED THEREFOR |
| US4869263A (en) * | 1988-02-04 | 1989-09-26 | Cardiometrics, Inc. | Device and method for measuring volumetric blood flow in a vessel |
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| FR2582213A1 (en) | 1986-11-28 |
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| DE3615341A1 (en) | 1986-11-27 |
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