CA2023355A1 - Epidural oxygen sensor - Google Patents
Epidural oxygen sensorInfo
- Publication number
- CA2023355A1 CA2023355A1 CA002023355A CA2023355A CA2023355A1 CA 2023355 A1 CA2023355 A1 CA 2023355A1 CA 002023355 A CA002023355 A CA 002023355A CA 2023355 A CA2023355 A CA 2023355A CA 2023355 A1 CA2023355 A1 CA 2023355A1
- Authority
- CA
- Canada
- Prior art keywords
- photodetector
- light emitting
- emitting diodes
- sensor
- skull
- 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.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
- A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
- A61B5/031—Intracranial pressure
Abstract
EPIDURAL OXYGEN SENSOR
Abstract of the Disclosure:
A sensor for measuring the oxygen saturation of blood flow within the skull is described. In a first embodiment the sensor comprises a photodetector and a pair of light emitting diodes surface mounted near the end of a length of flexible printed wiring. The sensor is hermetically sealed by a coating of rubber or polymeric material which has an optical window over the photodetector and light emitting diodes. The sensor is inserted through a burr hole drilled in the skull and slides between the skull and the dura of the brain. The light emitting diodes are pulsed to illuminate blood within the dura and brain with light, and light reflected by the blood is received by the photodetector and converted to electrical signals. The signals are processed by a pulse oximeter to provide an indication of blood saturation. In a second embodiment the photodetector and light emitting diodes are mounted at the end of a core of compressible foam extending from the end of a hollow bone screw. As the bone screw is screwed into a burr hole in the skull the photodetector and light emitting diodes will contact the dura and the foam will compress to maintain optical contact between the electrical components and the dura. Light from the diodes is reflected by blood in the dura and brain, received by the photodetector, and the resultant electrical signals are processed by the pulse oximeter.
Abstract of the Disclosure:
A sensor for measuring the oxygen saturation of blood flow within the skull is described. In a first embodiment the sensor comprises a photodetector and a pair of light emitting diodes surface mounted near the end of a length of flexible printed wiring. The sensor is hermetically sealed by a coating of rubber or polymeric material which has an optical window over the photodetector and light emitting diodes. The sensor is inserted through a burr hole drilled in the skull and slides between the skull and the dura of the brain. The light emitting diodes are pulsed to illuminate blood within the dura and brain with light, and light reflected by the blood is received by the photodetector and converted to electrical signals. The signals are processed by a pulse oximeter to provide an indication of blood saturation. In a second embodiment the photodetector and light emitting diodes are mounted at the end of a core of compressible foam extending from the end of a hollow bone screw. As the bone screw is screwed into a burr hole in the skull the photodetector and light emitting diodes will contact the dura and the foam will compress to maintain optical contact between the electrical components and the dura. Light from the diodes is reflected by blood in the dura and brain, received by the photodetector, and the resultant electrical signals are processed by the pulse oximeter.
Description
2 ~ ~ 3 3 ~ ~
_PIDURAL OXYGEN SENSOR
This invention relates to sensors for determining the o~ygen saturation of tissues within the skull and, in particular, to such sensor which are placed epidurally through the skull to measure oxygen saturation.
During neurological and neurologically related surgical procedures it is oftentimes desirable to continuously monitor the oxygenation of blood which is supplied to the brain. Frequently access is gained to the brain through a borehole in the skull, and a sensor which measures oxygenation can then be inserteB through such a borehole. A sensor should then exhibit numerous design and performance criteria in order to operate satisfactorily in this environment. The sensor must be capable of insertion through the borehole so as to contact tissue where oxygen saturation is to be measured. The sensor must be soft so that it does not damage neurological tissue, yet be sufficiently rigid in certain dimensions so that it can be maneuvered from outside the s~ull. It also must be sized to fit inside the borehole and in the location where measurements are to be taken.
Furthermore, the sensor must be designed so as to eliminate detection of ambient light which will interfere with detection of the desired optical signals. The sensor must also prevent the detection of directly transmitted light from the light source of the sensor.
In accordance with the principles of the present invention, an optical sensor is provided for epidural measurement of blood oxygenation. In a first embodiment the sensor comprises a pair of light emitting diodes (LED's) which emit light at two predetermined wavelengths. The sensor also includes a photodetector for ~233;~
receiving light emitted by the LED's which has been reflected from adjacent blood perfused tissue. The LE~'s and the photodetector are mounted on fle~ible printed wiring which trans~its signals to the LED's and from the photodiode. The components are encapsulated in a soft polymer which is biocompatible. The resultant sensor is thus capable of operation in an epidural environment, and is further capable of being maneuvered into the desired position for epidural measurements.
In a second embodiment the LED's and photodetector are located in a hollow bo~e screw, with the components opposing the tissue from which measurements are to be taken. The components are bac~ed by a soft polymer which will compress under gentle pressure as the bone screw is tightened to cause the components to contact the dura.
In the drawings:
FIGURE 1 illustrates a cross-sectional view of the use of an epidural oxygenation sensor constructed in accordance with the present invention FIGURE 2 is a side cross-sectional view of an epidural o~ygenation sensor constructed in accordance with the principles of the present invention;
FIGURE 2a is a perspective view of an epidural oxygenation sensor constructed in accordance with the principles of the present invention;
FIGURES 3a-3c are cross-sectional views of different embodiments of epidural oxygenation sensors of the present invention;
2~33~
FIGURES 4a-6c are plan views of different placements of LED~s and photodiodes of epidural oxygenation sensors of the present invention;
FIGURE 7 is an electrical schematic of the components of the epidural o~ygenation sensor of FIGURE 2; and FIGURES 8a-8c are cross-sectional, top, and bottom views of an epidural oxygenation sensor mounted in a hollow bone screw.
Referring first to FIGURE 1, a skull is shown in which a burr hole 12 has been drilled. Underlying the skull is the dura 16 which encases the brain, and beneath the dura is the cerebrum 14. An epidural osygenation sensor 20 is inserted through the burr hole 12 for measurement of the o~ygenation of blood flowing in the dura 16. The sensor 20 is inserted through the burr hole and slides between the skull 10 and the dura 16, where it is shielded from ambient light entering the burr hole. At the distal end of the sensor 20 is a photodetector 24 and LED's 22 which face the dura through optical windows in the sensor. The photodetector and LED's are mounted on flexible printed wiring which is connected to a sensor cable 26. The sensor cable is connected to a pulse o~imeter (not shown), which provides drive pulses for the LED's, receives electrical signals from the photodetector, and processes the received electrical signals to produce an indication of the oxygen saturation of blood in the dura. The sensor is operated in a reflective mode, whereby light a~
different wavelengths emitted by the LED's is reflected by the blood in the dura and the reflected light is received by the photodetector.
As shown in FIGURE 2, the sensor 20 comprises a 2Q233~
photodetector 24 and an adjacent pair of L~D's 22a and 22b which are surface mounted to leads of fle~ible printed wiring 28 such as 0.001 inch Kapton~ wiring. The use of surface mounted components and the printed wiring provide a thin sens~r which minimizes cerebral compression.
Separating the LED's and the photodetector is a light barrier 25 which prevents the direct transmission of light from the LED's to the photodetectcr. The light barrier may be provided by an opaque epoxy material, but in a preferred embodiment the light barrier is formed of a thin sheet of copper foil. The copper foil not only effectively blocks light from the LED's, but is also connected to a grounded lead of the flexible printed wiring~ The copper foil thus shields the photodetector from radio frequency interference such as that emanated during pulsing of the LED's.
The foregoing components are encapsulated by a soft coating 30 of silicone rubber or polyurethane material.
The soft coating smoothly rounds the corners and edges of the sensor which prevents injury to the dura by the sensor. The coating also hermetically seals the components from moisture and other environmental factors.
The coating 30 is optically transmissive to light at the wavelengths of the LED's where it overlies the lower surfaces of the photodetector and the LED's from which light is transmitted and received ~y these c~mponents.
FIGURE 2a is a perspective view of the sensor 20 of 30 FIGURE 2, referenced to ~, y, and z a~es. As mentioned above, the coating 30 provides the sensor with a smooth, gently rounded profile such as the rounded distal end 27.
The sensor is relatively stiff along the portion of the printed wiring where the components are mounted to maintain their relative alignment. In the x dimension the 23~3~
sensor is fairly stiff so that it may be inserted and guided beneath the skull and in contact with the dura. In the z dimension the sensor is stiff to provide maneuverability during placement of the sensor. In the y dimension the sensor proximal the components is fleYible to curve through the burr hole and under the skull, which may have a thickness of 2 to 20 mm depending upon the patient.
In order to be capable of sliding between the skull and the dura the sensor should be thin in the y dimension so as not to injure the patient. Preferably the sensor thickness in this dimension should be not greater than 4 mm, and most preferably not greater than 2.5 mm. The sensor should also be not less than one millimeter in thickness to maintain continuous contact with the dura.
This will reduce the occurrence of motion artifacts, as the dura can move as much as ~ mm away from the skull during hyperventilation of the patient, for instance.
In the embodiment of FIGURE 2 the photodetector 24 is located toward the distal end 27 of the sensor with respect to the LED~s 22. This distal placement of the photodetector keeps the photodetector well removed from the burr hole and ambient light passing through the burr hole. FIGURES 3a-3c show other component orientations which may be employed in different sensor embodiments. In FIGURE 3a the LED's 22' are canted toward the dura where the dura overlies the photodetector 24, which improves the efficiency of light reflectance. The canted LED's are supported by a filler of the coating material 30. In FIGURE 3b two pairs of LED's 22~ are located on either side of the phototdetector 24 to illuminate the dura from both sides of the photodetector. In FIGURE 3c the pair of LED's 22 is centrally located between a pair of ~ ~ ~ 3 ~ 3 ~
photodetectors 24~, the latter being canted toward the area of the dura illuminated above the LED's.
It is desirable for the optical windows of the components which facs the dura to be as large as possible so as to ma~imize optical transmission efficiency.
Opposing this desire is the constraint that the sensor must be sized to fit through the burr hole in the skull.
To determine the largest components which may fit through a given burr hole diameter, rectanqular configurations of components may be calculated which are capable of fitting through the burr hole. FIGURES 4a-6c show component configurations which can fit through a 14 mm diameter burr hole. FIGURES 4a-4c show plan views of component layouts f~or the single photodetector and pair of LED's employed in the sensors oE FIGURES 2 and 3a. In FIGURE 4a the LED's 22' and the photodetector are arranged in a layout which measures 8.2 mm by 6.3 mm. In FIGURE 4b the rectangular layout measures 10.5 mm by 5.3 mm, and in FIGURE 4c the rectangular layout measures 9.3 mm by 5.7 mm. In each layout the coating material 30 is shown in the area outside the boundaries of the electrical components.
FIGURES 5a-5c show component layouts for a 14 mm diameter burr hole using two pairs of LED's 22~ and one photodetector 24. In FIGURE 5a the rectangular layout measures 10.8 mm by 7.0 mm; in FIGURE 5b the layout measures 13.0 mm by 5.5 mm; and in FIGURE 5c the alyout measures 8.2 mm by 7.3 mm. In a similar manner, FIGURES
6a-6c show component layouts using two photodetectors 24' and one or two pairs of LED's 22 or 22~. In FIGURE 6a the rectangular layout measures 8.1 mm by 6.8 mm; in FIGURE 6b the layout measures 11.5 mm by 6.8 mm; and in FIGURE 6c the layout measures 8.6 mm by 7.5 mm.
2~3~
In FIGURES 4a-6c each LED pair had an area of 3.0 mm by 4.2 mm. The photodetectors in FIGURES 6a and 6c had an iarea of 2.25 mm by 6.25 mm. In the remaining layouts the photodetectors each had an area of 4.0 mm by 6.25 mm.
FIGURE 7 is an electrical schematic of the sensor 20 of FIGURE 2. The two LED's 22a and 22b are connected in parallel and are parallelled by back-biased diodes 23 and 25. The anodes of each pair of components are connected to respective resistors of values chosen in correspondence with the drive current to be supplied to the ~ED's. The connected cathodes of the LED's are likewise coupled to a biasing resistor. The resistors may be mounted in line with the flexible printed wiring, such as the points 32a-32d at which the wiring joins the cable to the pulse o~imeter monitor.
FIGURES 8a-8c illustrate a further embodiment of an epidural sensor in which the sensor components are located in a hollow bone screw 40. The screw 40 is threaded as indicated at 44 to screw into the s~ull, and the head of the screw has a slot 42 to turn the screw with an adjustment instrument as more clearly shown in the top plan view of FIGURE 8b. A photodetector 24 and a pair of LED's 22 are located at the bottom of a core of soft, compressible foam material 52 in the center of the screw, as shown in the bottom plan ~iew of FIGURE 8c. Above the compressible foam 52 the center of the screw is filled with a firm filling 50 of silicone rubber or polyurethane. The electrical leads 26~ from the LED's and photodetector pass through the foam material 52 and the filling 50 and e~it through the top of the hollow screw as shown in FIGURE 8c.
In use of the sensor embodiment of FIGURES 8a-8c, a hole is drilled in the s~ull into which the bone screw 40 ls screwed. As the bone screw is screwed into the skull, l:he oximeter monitor is continuously monitored for the onset of oxygen saturation readings. When the bottom of the screw with the sensor components contacts the dura, oxygen readings will commence, and will initially occur erratically. As the bone screw is slowly turned the sensor components will make better contact with the dura and the signal quality will improve. The contact between the sensor components and the dura is induced in a gentle manner by the compressible foam 52, which will readily compress as the components ma~e contact with the dura to prevent damage to the dura. When consistent readings occur no further turning of the screw is necessary, as the sensor components are in good surface contact with the dura and will gently ride on the dura due to the compressibility of the foam 52. This hollow bone screw embodiment is desirable for its ability to completely block ambient light from the sensor components and by plugging the burr hole with the bone screw infection of the dura is retarded. The sensor can be safely left in place in the burr hole for extended periods of time.
_PIDURAL OXYGEN SENSOR
This invention relates to sensors for determining the o~ygen saturation of tissues within the skull and, in particular, to such sensor which are placed epidurally through the skull to measure oxygen saturation.
During neurological and neurologically related surgical procedures it is oftentimes desirable to continuously monitor the oxygenation of blood which is supplied to the brain. Frequently access is gained to the brain through a borehole in the skull, and a sensor which measures oxygenation can then be inserteB through such a borehole. A sensor should then exhibit numerous design and performance criteria in order to operate satisfactorily in this environment. The sensor must be capable of insertion through the borehole so as to contact tissue where oxygen saturation is to be measured. The sensor must be soft so that it does not damage neurological tissue, yet be sufficiently rigid in certain dimensions so that it can be maneuvered from outside the s~ull. It also must be sized to fit inside the borehole and in the location where measurements are to be taken.
Furthermore, the sensor must be designed so as to eliminate detection of ambient light which will interfere with detection of the desired optical signals. The sensor must also prevent the detection of directly transmitted light from the light source of the sensor.
In accordance with the principles of the present invention, an optical sensor is provided for epidural measurement of blood oxygenation. In a first embodiment the sensor comprises a pair of light emitting diodes (LED's) which emit light at two predetermined wavelengths. The sensor also includes a photodetector for ~233;~
receiving light emitted by the LED's which has been reflected from adjacent blood perfused tissue. The LE~'s and the photodetector are mounted on fle~ible printed wiring which trans~its signals to the LED's and from the photodiode. The components are encapsulated in a soft polymer which is biocompatible. The resultant sensor is thus capable of operation in an epidural environment, and is further capable of being maneuvered into the desired position for epidural measurements.
In a second embodiment the LED's and photodetector are located in a hollow bo~e screw, with the components opposing the tissue from which measurements are to be taken. The components are bac~ed by a soft polymer which will compress under gentle pressure as the bone screw is tightened to cause the components to contact the dura.
In the drawings:
FIGURE 1 illustrates a cross-sectional view of the use of an epidural oxygenation sensor constructed in accordance with the present invention FIGURE 2 is a side cross-sectional view of an epidural o~ygenation sensor constructed in accordance with the principles of the present invention;
FIGURE 2a is a perspective view of an epidural oxygenation sensor constructed in accordance with the principles of the present invention;
FIGURES 3a-3c are cross-sectional views of different embodiments of epidural oxygenation sensors of the present invention;
2~33~
FIGURES 4a-6c are plan views of different placements of LED~s and photodiodes of epidural oxygenation sensors of the present invention;
FIGURE 7 is an electrical schematic of the components of the epidural o~ygenation sensor of FIGURE 2; and FIGURES 8a-8c are cross-sectional, top, and bottom views of an epidural oxygenation sensor mounted in a hollow bone screw.
Referring first to FIGURE 1, a skull is shown in which a burr hole 12 has been drilled. Underlying the skull is the dura 16 which encases the brain, and beneath the dura is the cerebrum 14. An epidural osygenation sensor 20 is inserted through the burr hole 12 for measurement of the o~ygenation of blood flowing in the dura 16. The sensor 20 is inserted through the burr hole and slides between the skull 10 and the dura 16, where it is shielded from ambient light entering the burr hole. At the distal end of the sensor 20 is a photodetector 24 and LED's 22 which face the dura through optical windows in the sensor. The photodetector and LED's are mounted on flexible printed wiring which is connected to a sensor cable 26. The sensor cable is connected to a pulse o~imeter (not shown), which provides drive pulses for the LED's, receives electrical signals from the photodetector, and processes the received electrical signals to produce an indication of the oxygen saturation of blood in the dura. The sensor is operated in a reflective mode, whereby light a~
different wavelengths emitted by the LED's is reflected by the blood in the dura and the reflected light is received by the photodetector.
As shown in FIGURE 2, the sensor 20 comprises a 2Q233~
photodetector 24 and an adjacent pair of L~D's 22a and 22b which are surface mounted to leads of fle~ible printed wiring 28 such as 0.001 inch Kapton~ wiring. The use of surface mounted components and the printed wiring provide a thin sens~r which minimizes cerebral compression.
Separating the LED's and the photodetector is a light barrier 25 which prevents the direct transmission of light from the LED's to the photodetectcr. The light barrier may be provided by an opaque epoxy material, but in a preferred embodiment the light barrier is formed of a thin sheet of copper foil. The copper foil not only effectively blocks light from the LED's, but is also connected to a grounded lead of the flexible printed wiring~ The copper foil thus shields the photodetector from radio frequency interference such as that emanated during pulsing of the LED's.
The foregoing components are encapsulated by a soft coating 30 of silicone rubber or polyurethane material.
The soft coating smoothly rounds the corners and edges of the sensor which prevents injury to the dura by the sensor. The coating also hermetically seals the components from moisture and other environmental factors.
The coating 30 is optically transmissive to light at the wavelengths of the LED's where it overlies the lower surfaces of the photodetector and the LED's from which light is transmitted and received ~y these c~mponents.
FIGURE 2a is a perspective view of the sensor 20 of 30 FIGURE 2, referenced to ~, y, and z a~es. As mentioned above, the coating 30 provides the sensor with a smooth, gently rounded profile such as the rounded distal end 27.
The sensor is relatively stiff along the portion of the printed wiring where the components are mounted to maintain their relative alignment. In the x dimension the 23~3~
sensor is fairly stiff so that it may be inserted and guided beneath the skull and in contact with the dura. In the z dimension the sensor is stiff to provide maneuverability during placement of the sensor. In the y dimension the sensor proximal the components is fleYible to curve through the burr hole and under the skull, which may have a thickness of 2 to 20 mm depending upon the patient.
In order to be capable of sliding between the skull and the dura the sensor should be thin in the y dimension so as not to injure the patient. Preferably the sensor thickness in this dimension should be not greater than 4 mm, and most preferably not greater than 2.5 mm. The sensor should also be not less than one millimeter in thickness to maintain continuous contact with the dura.
This will reduce the occurrence of motion artifacts, as the dura can move as much as ~ mm away from the skull during hyperventilation of the patient, for instance.
In the embodiment of FIGURE 2 the photodetector 24 is located toward the distal end 27 of the sensor with respect to the LED~s 22. This distal placement of the photodetector keeps the photodetector well removed from the burr hole and ambient light passing through the burr hole. FIGURES 3a-3c show other component orientations which may be employed in different sensor embodiments. In FIGURE 3a the LED's 22' are canted toward the dura where the dura overlies the photodetector 24, which improves the efficiency of light reflectance. The canted LED's are supported by a filler of the coating material 30. In FIGURE 3b two pairs of LED's 22~ are located on either side of the phototdetector 24 to illuminate the dura from both sides of the photodetector. In FIGURE 3c the pair of LED's 22 is centrally located between a pair of ~ ~ ~ 3 ~ 3 ~
photodetectors 24~, the latter being canted toward the area of the dura illuminated above the LED's.
It is desirable for the optical windows of the components which facs the dura to be as large as possible so as to ma~imize optical transmission efficiency.
Opposing this desire is the constraint that the sensor must be sized to fit through the burr hole in the skull.
To determine the largest components which may fit through a given burr hole diameter, rectanqular configurations of components may be calculated which are capable of fitting through the burr hole. FIGURES 4a-6c show component configurations which can fit through a 14 mm diameter burr hole. FIGURES 4a-4c show plan views of component layouts f~or the single photodetector and pair of LED's employed in the sensors oE FIGURES 2 and 3a. In FIGURE 4a the LED's 22' and the photodetector are arranged in a layout which measures 8.2 mm by 6.3 mm. In FIGURE 4b the rectangular layout measures 10.5 mm by 5.3 mm, and in FIGURE 4c the rectangular layout measures 9.3 mm by 5.7 mm. In each layout the coating material 30 is shown in the area outside the boundaries of the electrical components.
FIGURES 5a-5c show component layouts for a 14 mm diameter burr hole using two pairs of LED's 22~ and one photodetector 24. In FIGURE 5a the rectangular layout measures 10.8 mm by 7.0 mm; in FIGURE 5b the layout measures 13.0 mm by 5.5 mm; and in FIGURE 5c the alyout measures 8.2 mm by 7.3 mm. In a similar manner, FIGURES
6a-6c show component layouts using two photodetectors 24' and one or two pairs of LED's 22 or 22~. In FIGURE 6a the rectangular layout measures 8.1 mm by 6.8 mm; in FIGURE 6b the layout measures 11.5 mm by 6.8 mm; and in FIGURE 6c the layout measures 8.6 mm by 7.5 mm.
2~3~
In FIGURES 4a-6c each LED pair had an area of 3.0 mm by 4.2 mm. The photodetectors in FIGURES 6a and 6c had an iarea of 2.25 mm by 6.25 mm. In the remaining layouts the photodetectors each had an area of 4.0 mm by 6.25 mm.
FIGURE 7 is an electrical schematic of the sensor 20 of FIGURE 2. The two LED's 22a and 22b are connected in parallel and are parallelled by back-biased diodes 23 and 25. The anodes of each pair of components are connected to respective resistors of values chosen in correspondence with the drive current to be supplied to the ~ED's. The connected cathodes of the LED's are likewise coupled to a biasing resistor. The resistors may be mounted in line with the flexible printed wiring, such as the points 32a-32d at which the wiring joins the cable to the pulse o~imeter monitor.
FIGURES 8a-8c illustrate a further embodiment of an epidural sensor in which the sensor components are located in a hollow bone screw 40. The screw 40 is threaded as indicated at 44 to screw into the s~ull, and the head of the screw has a slot 42 to turn the screw with an adjustment instrument as more clearly shown in the top plan view of FIGURE 8b. A photodetector 24 and a pair of LED's 22 are located at the bottom of a core of soft, compressible foam material 52 in the center of the screw, as shown in the bottom plan ~iew of FIGURE 8c. Above the compressible foam 52 the center of the screw is filled with a firm filling 50 of silicone rubber or polyurethane. The electrical leads 26~ from the LED's and photodetector pass through the foam material 52 and the filling 50 and e~it through the top of the hollow screw as shown in FIGURE 8c.
In use of the sensor embodiment of FIGURES 8a-8c, a hole is drilled in the s~ull into which the bone screw 40 ls screwed. As the bone screw is screwed into the skull, l:he oximeter monitor is continuously monitored for the onset of oxygen saturation readings. When the bottom of the screw with the sensor components contacts the dura, oxygen readings will commence, and will initially occur erratically. As the bone screw is slowly turned the sensor components will make better contact with the dura and the signal quality will improve. The contact between the sensor components and the dura is induced in a gentle manner by the compressible foam 52, which will readily compress as the components ma~e contact with the dura to prevent damage to the dura. When consistent readings occur no further turning of the screw is necessary, as the sensor components are in good surface contact with the dura and will gently ride on the dura due to the compressibility of the foam 52. This hollow bone screw embodiment is desirable for its ability to completely block ambient light from the sensor components and by plugging the burr hole with the bone screw infection of the dura is retarded. The sensor can be safely left in place in the burr hole for extended periods of time.
Claims (18)
1. A sensor for measuring cerebral oxygen saturation through a burr hole in the skull by optical reflectance comprising:
a length of flexible wiring having a distal end and a proximal end which is to be connected to an oximeter;
a photodetector electrically connected to said flexible wiring in the proximity of said distal end;
a pair of light emitting diodes connected to said flexible wiring adjacent to said photodiode; and a coating encapsulating said photodetector, said light emitting diodes, and said flexible wiring in the proximity of said photodetector and light emitting diodes, said coating including optical windows where said coating overlies the optical windows of said photodetector and light emitting diodes which is transmissive to light at the wavelengths of said light emitting diodes.
a length of flexible wiring having a distal end and a proximal end which is to be connected to an oximeter;
a photodetector electrically connected to said flexible wiring in the proximity of said distal end;
a pair of light emitting diodes connected to said flexible wiring adjacent to said photodiode; and a coating encapsulating said photodetector, said light emitting diodes, and said flexible wiring in the proximity of said photodetector and light emitting diodes, said coating including optical windows where said coating overlies the optical windows of said photodetector and light emitting diodes which is transmissive to light at the wavelengths of said light emitting diodes.
2. The sensor of Claim 1, further including a light barrier which shields said photodetector from the direct reception of light from said light emitting diodes.
3. The sensor of Claim 2, wherein said light barrier comprises opaque epoxy.
4. The sensor of Claim 2, wherein said light barrier comprises metal foil.
5. The sensor of Claim 1, wherein said flexible wiring comprises flexible printed wiring.
6. The sensor of Claim 1, wherein said coating is silicone rubber.
7. The sensor of Claim 1, wherein said coating is polyurethane.
8. The sensor of Claim 1, wherein the optical window of said light emitting diodes is canted toward the area above said photodetector.
9. The sensor of Claim 1, further comprising a second pair of light emitting diodes located adjacent said photodetector and on the opposite side of said photodetector as said first-named pair of light emitting diodes.
10. The sensor of Claim 1, further comprising a second photodetector located adjacent said light emitting diodes on the opposite side of said light emitting diodes as said first-named photodetector.
11. The sensor of Claim 10, wherein said photodetectors are canted toward the area above said light emitting diodes.
12. The sensor of Claim 1, wherein said photodetector and said light emitting diodes occupy an area sized to fit through a burr hole of a given diameter.
13. A sensor for measuring cerebral oxygen saturation through a burr hole in the skull by optical reflectance comprising:
a hollow bone screw;
a core of compressive material located in said hollow bone screw and having an upper surface oriented toward the top of said bone screw and a lower surface oriented toward the bottom of said bone screw; and a photodetector and a pair of light emitting diodes located at said lower surface of said core of compressive material, wherein electrical connection is made to said photodetector and said light emitting diodes through said hollow bone screw.
a hollow bone screw;
a core of compressive material located in said hollow bone screw and having an upper surface oriented toward the top of said bone screw and a lower surface oriented toward the bottom of said bone screw; and a photodetector and a pair of light emitting diodes located at said lower surface of said core of compressive material, wherein electrical connection is made to said photodetector and said light emitting diodes through said hollow bone screw.
14. The sensor of Claim 13, further comprising a core of relatively less compressive material located within said bone screw above said upper surface of said compressive core.
15. The sensor of Claim 13, wherein a portion of said core of compressive material extends out from the lower end of said hollow bone screw.
16. A method of epidurally sensing oxygen saturation comprising the steps of:
drilling a burr hole in a skull;
inserting a length of flexible wiring having a photodetector and a pair of light emitting diodes mounted in the proximity of the distal end of said wiring through said burr hole and between the skull and the dura, with the optical windows of said photodetector and said light emitting diodes opposing the dura;
energizing said light emitting diodes, and receiving electrical signals from said photodetector resulting from the reception of reflected light emanating from said diodes, by way of said flexible wiring; and processing said electrical signals to produce an indication of blood oxygen saturation.
drilling a burr hole in a skull;
inserting a length of flexible wiring having a photodetector and a pair of light emitting diodes mounted in the proximity of the distal end of said wiring through said burr hole and between the skull and the dura, with the optical windows of said photodetector and said light emitting diodes opposing the dura;
energizing said light emitting diodes, and receiving electrical signals from said photodetector resulting from the reception of reflected light emanating from said diodes, by way of said flexible wiring; and processing said electrical signals to produce an indication of blood oxygen saturation.
17. A method of sensing oxygen saturation of blood flow within the skull comprising the steps of:
drilling a burr hole in a skull;
screwing a hollow bone screw into said burr hole which has a photodetector and a pair of light emitting diodes located at the distal end of the screw;
ceasing to screw the bone screw into the skull when said photodetector and light emitting diodes are in optical contact with tissue within the skull and signals representative of blood oxygenation are received from said photodetector.
drilling a burr hole in a skull;
screwing a hollow bone screw into said burr hole which has a photodetector and a pair of light emitting diodes located at the distal end of the screw;
ceasing to screw the bone screw into the skull when said photodetector and light emitting diodes are in optical contact with tissue within the skull and signals representative of blood oxygenation are received from said photodetector.
18. A method of sensing oxygen saturation of blood flow within the skull comprising the steps of:
drilling a burr hole in a skull;
screwing a hollow bone screw into said burr hole which has a photodetector and a pair of light emitting diodes mounted on a core of compressive material extending from the distal end of the screw;
ceasing to screw the bone screw into the skull when said compressive material compresses to maintain said photodetector and light emitting diodes in optical contact with tissue within the skull and signals representative of blood oxygenation are received from said photodetector.
drilling a burr hole in a skull;
screwing a hollow bone screw into said burr hole which has a photodetector and a pair of light emitting diodes mounted on a core of compressive material extending from the distal end of the screw;
ceasing to screw the bone screw into the skull when said compressive material compresses to maintain said photodetector and light emitting diodes in optical contact with tissue within the skull and signals representative of blood oxygenation are received from said photodetector.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/394,997 US5024226A (en) | 1989-08-17 | 1989-08-17 | Epidural oxygen sensor |
| US394,997 | 1995-02-27 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2023355A1 true CA2023355A1 (en) | 1991-02-18 |
Family
ID=23561272
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002023355A Abandoned CA2023355A1 (en) | 1989-08-17 | 1990-08-15 | Epidural oxygen sensor |
Country Status (10)
| Country | Link |
|---|---|
| US (2) | US5024226A (en) |
| EP (2) | EP0413588B1 (en) |
| JP (1) | JPH03228746A (en) |
| KR (1) | KR100191230B1 (en) |
| AT (2) | ATE134849T1 (en) |
| CA (1) | CA2023355A1 (en) |
| DE (2) | DE69025673T2 (en) |
| DK (2) | DK0413588T3 (en) |
| ES (2) | ES2097063T3 (en) |
| GR (1) | GR1001029B (en) |
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- 1989-08-17 US US07/394,997 patent/US5024226A/en not_active Expired - Fee Related
-
1990
- 1990-08-15 CA CA002023355A patent/CA2023355A1/en not_active Abandoned
- 1990-08-16 DE DE69025673T patent/DE69025673T2/en not_active Expired - Fee Related
- 1990-08-16 ES ES95200028T patent/ES2097063T3/en not_active Expired - Lifetime
- 1990-08-16 AT AT90309019T patent/ATE134849T1/en not_active IP Right Cessation
- 1990-08-16 DE DE69029869T patent/DE69029869T2/en not_active Expired - Fee Related
- 1990-08-16 ES ES90309019T patent/ES2084662T3/en not_active Expired - Lifetime
- 1990-08-16 AT AT95200028T patent/ATE148323T1/en not_active IP Right Cessation
- 1990-08-16 DK DK90309019.9T patent/DK0413588T3/en active
- 1990-08-16 EP EP90309019A patent/EP0413588B1/en not_active Expired - Lifetime
- 1990-08-16 EP EP95200028A patent/EP0651968B1/en not_active Expired - Lifetime
- 1990-08-16 GR GR900100617A patent/GR1001029B/en unknown
- 1990-08-16 DK DK95200028.9T patent/DK0651968T3/da active
- 1990-08-17 JP JP2218009A patent/JPH03228746A/en active Pending
- 1990-08-17 KR KR1019900012643A patent/KR100191230B1/en not_active IP Right Cessation
- 1990-11-13 US US07/612,744 patent/US5127407A/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| DK0413588T3 (en) | 1996-07-22 |
| JPH03228746A (en) | 1991-10-09 |
| DK0651968T3 (en) | 1997-02-24 |
| KR100191230B1 (en) | 1999-06-15 |
| DE69029869D1 (en) | 1997-03-13 |
| DE69029869T2 (en) | 1997-06-05 |
| DE69025673T2 (en) | 1996-08-01 |
| KR910004155A (en) | 1991-03-28 |
| EP0651968A1 (en) | 1995-05-10 |
| GR1001029B (en) | 1993-03-31 |
| ATE134849T1 (en) | 1996-03-15 |
| EP0413588B1 (en) | 1996-03-06 |
| EP0413588A2 (en) | 1991-02-20 |
| EP0651968B1 (en) | 1997-01-29 |
| ATE148323T1 (en) | 1997-02-15 |
| ES2097063T3 (en) | 1997-03-16 |
| GR900100617A (en) | 1991-12-30 |
| DE69025673D1 (en) | 1996-04-11 |
| ES2084662T3 (en) | 1996-05-16 |
| EP0413588A3 (en) | 1991-10-23 |
| US5024226A (en) | 1991-06-18 |
| US5127407A (en) | 1992-07-07 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| FZDE | Discontinued |