System and method for measuring the pressure of a fluid system within a patient

Abstract

A pressure sensing apparatus has a pressure sensor component that includes a pressure sensing port, a pressure sensor for sensing a pressure of a fluid in the pressure sensing port, and a digital processor communicating with the pressure sensor for performing calculations involving fluid pressures sensed. The pressure sensing apparatus further includes a first chamber in fluid contact with the pressure sensing port, a second chamber fluidically connectable with a patient's cerebrospinal fluid system, and a membrane located between the first and second chambers so as to transmit fluid pressure from the second chamber to the first chamber.

Claims

1. A method for measuring a pressure of a cerebrospinal fluid system in a patient comprising: providing a pressure sensing system having a sterile portion for connecting to a patient's cerebrospinal fluid system and a non-sterile portion, the non-sterile portion including a pressure sensor component having a pressure sensor and a processor for analyzing cerebrospinal fluid pressures measured by the pressure sensor; connecting the sterile portion to the patient's cerebrospinal fluid system through a puncture site, the sterile portion providing access to the cerebrospinal fluid system outside of the patient's body; measuring the patient's cerebrospinal fluid pressure using the pressure sensor component and displaying the patient's cerebrospinal fluid pressure on the pressure sensor component.

2. The method of claim 1, wherein the pressure sensor component calculates a resting pressure based on fluid pressures measured.

3. The method of claim 1, wherein the sterile portion includes a bolus apparatus and the method further comprises injecting or withdrawing a bolus of known fluid volume to the patient's cerebrospinal fluid system while the pressure sensor component measures and displays the patient's cerebrospinal fluid pressure.

4. The method of claim 3, wherein the pressure sensor component calculates an output resistance based on fluid pressures measured.

5. The method of claim 3, wherein the pressure sensor component calculates a pressure volume index based on fluid pressures measured.

6. The method of claim 1, wherein the pressure sensor component has a pressure sensing port with the pressure sensor sensing a pressure of a fluid in the pressure sensing port; the non-sterile portion of the pressure sensing system includes a first chamber in fluid contact with the pressure sensing port; the sterile portion of the pressure sensing system includes a second chamber fluidically connectable with a patient's cerebrospinal fluid system; and the pressure sensing system further includes a membrane located between the first and second chambers so as to transmit fluid pressure from the second chamber to the first chamber.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) The invention will be more fully understood from the following detailed description taken in conjunction with the accompanying drawings, in which:

(2) FIG. 1 illustrates a system of the invention for measuring a pressure of a fluid system in a patient;

(3) FIG. 2 is diagrammatic view illustrating additional features of the system of FIG. 1;

(4) FIG. 3 illustrates a pressure sensor component of the invention; and

(5) FIG. 4 illustrates a pressure graph used to illustrate calculations made by the pressure sensor of FIG. 3.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

(6) A system 10 representative of one embodiment of the invention is presented in FIG. 1 as including a pressure sensor component 12 with integrated fluid dynamics assessment that can be coupled with a patient's 14 CSF system to measure and analyze the patient's CSF pressure, as well as methods for doing the same. As shown, the system is coupled to the patient's CSF system at a puncture site 16 which may represent a conventional lumbar tap. Tubing 18 fluidically couples the puncture site to a coupling element 20in the illustrated embodiment, a three-way stopcock. The three-way stopcock 20 couples tubing 18 with syringe 22 (through tubing 24) and a first chamber 26. First chamber 26 is separated from a second chamber 30 by a membrane 28 (internal to the system illustrated in FIG. 1) that is movable to allow pressure from a fluid in the first chamber to be transmitted to fluid in the second chamber. Second chamber 30 is in fluid communication with pressure sensor port 32 of pressure sensor component 12 where a pressure sensor of the pressure sensor component can measure the pressure of a fluid in the second chamber for analysis and display. Accordingly, system 10 can measure the pressure of fluid in the patient's CSF system by way of the fluid and pressure communication sequence from puncture site 16 to pressure sensor port 32.

(7) System 10 can be further described by reference to FIG. 2 which illustrates diagrammatically the system of FIG. 1. The patient's CSF system is illustrated by functional block 40 which is fluidically coupled to CSF Access Equipment 42. The CSF Access Equipment includes the elements necessary to tap into the patient's CSF system and provide access to that system outside of the patient's body. As noted above, this access is typically gained through a lumbar tap in which a large gage needle is used to access the CSF system in the space between the patient's vertebrae, often between the third and fourth lumbar vertebrae. As suggested in the Figure, however, this access could be gained using any variety of needle, catheter, stylet and/or connectors as might be appropriate for accessing the patient's CSF system. Further, if a system of the invention is deployed for use with a different fluid system of the patient, a person skilled in the art will recognize that access equipment suitable for coupling to that fluid system can be used within the spirit of the invention.

(8) CSF Access Equipment 42 can be fluidically coupled to Bolus Equipment 44 if desired for manipulation of the fluid within the system. The Bolus Equipment typically includes a syringe for the injection and/or withdrawal of fluid from the system. A three-way stopcock can also be employed to control the flow of fluid. A person of skill in the art will recognize that other equipment may be used, a bi-directional or infusion pump for example, to inject or withdraw fluid from the system.

(9) The elements so far described by reference to FIG. 2 fall within a sterile portion 46 of system 10. As these elements are exposed within the patient by virtue of the flow of fluid within the system, these element should be sterile as is well known in the art. The fluid flowing within the sterile portion of system 10 will generally include fluid from the patient's system being measured, in the illustrated embodiment CSF, and can also include other biocompatible fluids such as saline. Such biocompatible fluids can be used within the syringe to provide a bolus. Further, where fluidic coupling is long, especially between CSF Access Equipment 42 and Bolus Equipment 44 so as to make the positioning of the Bolus Equipment and the pressure sensor component more convenient for use, at least portions of the system may be filled with saline prior to connection with the patient to minimize CSF volume loss.

(10) The fluid in the sterile portion 46 of system 10 can be coupled through membrane 28 to the pressure sensor 48. In general, pressure sensor 48 will reside in a non-sterile portion 50 of system 10 as it is likely to be re-used from patient to patient and the system can be constructed so as to separate the non-sterile portion from contact with the patient's fluids. Typical high accuracy pressure sensors require fluid coupling, such that there is a vetted surface on the sensor. This sensor is often located in a protected area within a lumen that is not easily accessed (e.g., within pressure sensor port 32). The pressure sensor lumen can be filled with water (or other liquids such as oil or alcohol depending on the particular sensor embodiment used) for this purpose. Membrane 28 can be located so as to contact fluid in the sterile region 46 on one side, and fluid in the non-sterile region 50 on the other. Where membrane 28 is movable or flexible, changes in fluid pressure in the sterile portion of the system (including the patient's CSF system) are transmitted by movement of the membrane to the fluid in the non-sterile portion 50. These pressures can be read by pressure sensor 48.

(11) A pressure sensor component 12 for use with the invention can further be described by reference to FIG. 3. Pressure sensor component 12 can be a known hand-held fully integrated pressure sensor having a digital processor that can be configured to analyze the pressure signals provided in accordance with the description of FIGS. 1 and 2 above. Such known pressure sensors could include, for example, the Dwyer Instruments Series 477 handheld digital manometer available from Dwyer Instruments, Inc. of Michigan City, Ind., or the Fluke Model 717 or 718 pressure calibrators available from Fluke Corporation of Everett, Wash. Pressure sensor component 12 includes pressure sensor port 32, and also a second pressure sensor port 64 for pressure differential measurements. This second port can remain exposed to the atmosphere if it is not otherwise used. Pressure sensor component 12 also includes a display 60 for displaying pressure measurement results and analysis, and user input elements, buttons 62, for operating the component.

(12) Display 60 in FIG. 1 illustrates a graphical display of pressure measurements over time, while display 60 in FIG. 3 illustrates the current pressure 66 along with calculated values for the resting, baseline or starting pressure (Po) 70, the pressure-volume index (PVI) 72, and resistance to outflow (Ro) 74. The results are indicated to be for a third iteration (n=3) 68 of measurements. These CSF pressure dynamics testing results can yield information that can be used to confirm the probable diagnosis of Normal Pressure Hydrocephalus and aid in the selection of a shunt opening pressure for a shunt to be implanted in the patient.

(13) While the illustrated display shows outflow resistance and pressure-volume index values, and exemplary methods for calculating and using these values are described below, the invention described herein is not limited to this choice of parameters or particular methods of calculation. Pressure sensor component 12 can be programmed to calculate other pressure based parameters and also to calculate the aforementioned parameters in ways other than those disclosed herein. In fact, clinicians or researchers could develop new parameters to more accurately diagnose NPH or other fluid system abnormalities, the analysis of which using the systems and methods described herein is believed to fall within the present invention. In one embodiment of the present invention, pressure sensor component is programmable so as to allow a user to program the calculation of the user's own preferred parameters or to carry out the calculations using the user's preferred methods of calculation. Further information relating to the relationship between CSF abnormalities and pressure related parameters can be found in Shapiro K, Marmarou A, Shulman K, Characterisation of clinical CSF dynamics and neural axis compliance using the pressure-volume index, Annals of Neurology 7 (6) 508-514 (June 1980), which is incorporated herein by reference.

(14) The resting pressure, P.sub.o, can provide general information that may be used as an indicator for shunt opening pressure selection; its value can also used in further calculations as described below. The PVI can be calculated from the pressure change resulting from a rapid injection or withdrawal of fluid from the CSF space and has found widespread use both clinically and experimentally as a measure of lumped craniospinal compliance. The outflow resistance, R.sub.o, has been shown to be a good indicator of patents who will benefit from CSF shunting. In general, normal values for R.sub.o are generally about 1.5 to 4 mmHg/ml/min, while patients suffering from NPH generally have R.sub.o values of about 4 to 12.

(15) One exemplary approach to calculating these values using system 10 of FIG. 1, including pressure sensor component 12 as further illustrated in FIG. 3, can further be described by reference to FIG. 4. FIG. 4 provides a graph of pressure versus time that represents the patient's CSF pressure over time including the pressure response of the patient's CSF system to a bolus injection. The resting pressure, P.sub.o, can be seen on the graph at a time before the bolus injection. At a given time, a bolus of volume V.sub.o is added to the system, for example using the syringe 22 of FIG. 1. The bolus injection results in a sharp rise in pressure reaching a peak pressure of P.sub.p. The pressure drops over time from its peak and can be measured at a time t.sub.2, typically two minutes after bolus injection, to generate a pressure reading P.sub.2 that is indicative of the return trajectory of the patient's CSF pressure.

(16) With these variables known, the patient's pressure-volume index can be calculated as follows:
PVI=V.sub.o/Log(P.sub.p/P.sub.o)
and the CSF outflow resistance can be calculated as:
R.sub.o=t.sub.2P.sub.o/PVILog {(P.sub.2/P.sub.p) (P.sub.pP.sub.o)/(P.sub.2P.sub.o)}

(17) As noted above, the bolus injection, measurements and calculations may be performed in multiple iterations, with either individual iterations or mean values. In one embodiment, a user can select iterations for averaging, leaving out any apparently abnormal data.

(18) Pressure sensor component 12 can also provide user defined variables. For example, the following variables with the following exemplary default values can be set:

(19) TABLE-US-00001 Infusion Volume 4 cc Recovery Time 180 sec PVI Limit 13 ml P.sub.o Limit 30 mmHg P.sub.p Limit 30 mmHg
These values/limits can be user adjustable to conform to particular circumstances.

(20) Pressure sensor component 12 can also be configured to prompt a user through a measuring procedure. For example, with the pressure sensor component powered on, the user defined variables set as desired, and the system connected to a patient as illustrated in FIG. 1, the component will begin by displaying the resting pressure P.sub.o. Once P.sub.o is recorded, the pressure sensor component can prompt the user to infuse the system with a measured volume of fluid. The user can then begin the infusion, typically by infusing 4 cc of saline at approximately 1 cc/sec. The user can watch the real-time pressure display to confirm the absence of anomalous peaks during infusion. Once the infusion is complete and P.sub.p is recorded, the pressure sensor component can prompt the user to wait, typically for three minutes or until the current pressure is less than P.sub.o plus 2 mmHg, while the component measures P.sub.2. The pressure sensor component can then calculate P.sub.o, PVI, and R.sub.o for that iteration and display them to the user. Once the pressure reading has recovered from the infusion, the pressure sensor component can prompt the user to perform another iteration or disconnect the system from the patient. The user can select iterations to include or exclude from mean calculations, and mean values can be calculated and displayed.

(21) The pressure sensor component 12 illustrated in FIGS. 1 and 3 is shown as an integral handheld unit having a pressure sensor located within pressure sensor port 32, and all of the digital electronic components required to perform the calculations described above. A person skilled in the art will understand, however, that other configurations are possible. For example, the pressure sensor port 32, or only the sensor itself, could be fluidically coupled to second chamber 30 while maintaining electronic communication to a digital processing unit for performing desired display and calculation based on the pressure signal. Still further, the pressure sensor could be provided as part of the sterile portion 46 of system 10, making second chamber 30 unnecessary.

(22) Accordingly, the embodiments of the present invention are not limited by what has been particularly shown and described, except as indicated by the appended claims. All publications and references cited herein are expressly incorporated herein by reference in their entirety.