|Número de publicación||US20050209602 A1|
|Tipo de publicación||Solicitud|
|Número de solicitud||US 10/984,566|
|Fecha de publicación||22 Sep 2005|
|Fecha de presentación||9 Nov 2004|
|Fecha de prioridad||22 Mar 2004|
|También publicado como||CN1933792A, CN1933792B, EP1727500A1, EP1727500B1, US8029511, US20050209601, US20090076518, WO2005092249A1|
|Número de publicación||10984566, 984566, US 2005/0209602 A1, US 2005/209602 A1, US 20050209602 A1, US 20050209602A1, US 2005209602 A1, US 2005209602A1, US-A1-20050209602, US-A1-2005209602, US2005/0209602A1, US2005/209602A1, US20050209602 A1, US20050209602A1, US2005209602 A1, US2005209602A1|
|Inventores||Bruce Bowman, Robert Kohler, Erik Martz, Daniel Melink, Khin Myint, Michael Ahrens, Jean-Charles LeHuec, John Sherman, Scott Hook, Dennis Johnson, Qi-Bin Bao, Robert Hudgins|
|Cesionario original||Disc Dynamics, Inc.|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (63), Citada por (53), Clasificaciones (36), Eventos legales (1)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
The present application claims the benefit of U.S. Provisional Application Ser. No. 60/555,382 entitled MULTI-STAGE BIOMATERIAL INJECTION SYSTEM FOR SPINAL IMPLANTS filed on Mar. 22, 2004.
The present invention relates to a method and apparatus for filling an intervertebral disc space with an in situ curable biomaterial using a biomaterial injection system to form an implant device and to a method for replacing, in whole or in part, an intervertebral disc using the present method and apparatus.
The intervertebral discs, which are located between adjacent vertebrae in the spine, provide structural support for the spine as well as the distribution of forces exerted on the spinal column. An intervertebral disc consists of three major components: cartilage endplates, nucleus pulpous, and annulus fibrosus. The central portion, the nucleus pulpous or nucleus, is relatively soft and gelatinous; being composed of about 70 to 90% water. The nucleus pulpous has a high proteoglycan content and contains a significant amount of Type II collagen and chondrocytes. Surrounding the nucleus is the annulus fibrosus, which has a more rigid consistency and contains an organized fibrous network of approximately 40% Type I collagen, 60% Type II collagen, and fibroblasts. The annular portion serves to provide peripheral mechanical support to the disc, afford torsional resistance, and contain the softer nucleus while resisting its hydrostatic pressure.
Intervertebral discs, however, are susceptible to a number of injuries. Disc herniation occurs when the nucleus begins to extrude through an opening in the annulus, often to the extent that the herniated material impinges on nerve roots in the spine or spinal cord. The posterior and posterio-lateral portions of the annulus are most susceptible to attenuation or herniation, and therefore, are more vulnerable to hydrostatic pressures exerted by vertical compressive forces on the intervertebral disc. Various injuries and deterioration of the intervertebral disc and annulus fibrosus are discussed by Osti et al., Annular Tears and Disc Degeneration in the Lumbar Spine, J. Bone and Joint Surgery, 74-B(5), (1982) pp. 678-682; Osti et al., Annulus Tears and Intervertebral Disc Degeneration, Spine, 15(8) (1990) pp. 762-767; Kamblin et al., Development of Degenerative Spondylosis of the Lumbar Spine after Partial Discectomy, Spine, 20(5) (1995) pp. 599-607.
Many treatments for intervertebral disc injury have involved the use of nuclear prostheses or disc spacers. A variety of prosthetic nuclear implants are known in the art. For example, U.S. Pat. No. 5,047,055 (Bao et al.) teaches a swellable hydrogel prosthetic nucleus. Other devices known in the art, such as intervertebral spacers, use wedges between vertebrae to reduce the pressure exerted on the disc by the spine. Intervertebral disc implants for spinal fusion are known in the art as well, such as disclosed in U.S. Pat. Nos. 5,425,772 (Brantigan) and U.S. Pat. No. 4,834,757 (Brantigan).
Further approaches are directed toward fusion of the adjacent vertebrate, e.g., using a cage in the manner provided by Sulzer. Sulzer's BAK® Interbody Fusion System involves the use of hollow, threaded cylinders that are implanted between two or more vertebrae. The implants are packed with bone graft to facilitate the growth of vertebral bone. Fusion is achieved when adjoining vertebrae grow together through and around the implants, resulting in stabilization.
Apparatuses and/or methods intended for use in disc repair have also been described but none appear to have been further developed, and certainly not to the point of commercialization. See, for instance, French Patent Appl. No. FR 2 639 823 (Garcia) and U.S. Pat. No. 6,187,048 (Milner et al.). Both references differ in several significant respects from each other and from the apparatus and method described below. For instance, neither reference teaches switching the flow of biomaterial between discrete operating parameters or methods of detecting ruptures in the mold. Further, neither reference teaches shunting an initial portion of a curing biomaterial in the course of delivering the biomaterial to the disc space.
Prosthetic implants formed of biomaterials that can be delivered and cured in situ, using minimally invasive techniques to form a prosthetic nucleus within an intervertebral disc have been described in U.S. Pat. No. 5,556,429 (Felt) and U.S. Pat. No. 5,888,220 (Felt et al.), and U.S. Pat. Publication No. US 2003/0195628 (Felt et al.), the disclosures of which are incorporated herein by reference. The disclosed method includes, for instance, the steps of inserting a collapsed mold apparatus (which in a preferred embodiment is described as a “mold”) through an opening within the annulus, and filling the mold to the point that the mold material expands with a flowable biomaterial that is adapted to cure in situ and provide a permanent disc replacement. Related methods are disclosed in U.S. Pat. No. 6,224,630 (Bao et al.), entitled “Implantable Tissue Repair Device” and U.S. Pat. No. 6,079,868 (Rydell), entitled “Static Mixer”.
The present invention relates to a method and apparatus for filling an intervertebral disc space with an in situ curable biomaterial. The biomaterial injection system can be used, for example, to implant a prosthetic total disc, or a prosthetic disc nucleus, in a manner that leaves the surrounding disc tissue substantially intact. The phrase intervertebral disc prosthesis is used generically to refer to both of these variations. Optionally, the device and system of the invention are adapted for minimally invasive use. Various implant procedures, implant molds, and biomaterials related to intervertebral disc replacement suitable for use with the present invention are disclosed in U.S. Pat. No. 5,556,429 (Felt); U.S. Pat. No. 6,306,177 (Felt, et al.); U.S. Pat. No. 6,248,131 (Felt, et al.); U.S. Pat No. 5,795,353 (Felt); U.S. Pat. No. 6,079,868 (Rydell); U.S. Pat. No. 6,443,988 (Felt, et al.); U.S. Pat. No. 6,140,452 (Felt, et al.); U.S. Pat. No. 5,888,220 (Felt, et al.); U.S. Pat. No. 6,224,630 (Bao, et al.), and U.S. patent application Ser. Nos. 10/365,868 and 10/365,842, all of which are hereby incorporated by reference.
The present method of filling an intervertebral disc space with a flowable biomaterial includes the step of fluidly coupling a reservoir containing the flowable biomaterial to the intervertebral disc space. The delivery of the flowable biomaterial into the intervertebral disc space is controlled in accordance with a first operating parameter. At least one injection condition is monitored. The delivery of the flowable biomaterial is controlled in accordance with a second operating parameter in response to one or more of the injection conditions reaching a threshold level. The second operating parameter is maintained during at least a portion of the curing of the flowable biomaterial.
In one embodiment, the method includes fluidly coupling the reservoir containing the flowable biomaterial to a mold located in the intervertebral disc space. The first operating parameter delivers the flowable biomaterial to the mold so that the mold substantially fills the intervertebral disc space.
In another embodiment, a predetermined period of time is permitted to lapse after the at least one injection condition reaches the threshold level before initiating the second operating parameter. This dwell time comprises a third operating parameter. The length of this dwell time can be fixed or can vary from patient-to-patient.
The first operating parameter preferably applies sufficient pressure to rapidly fill the mold and to expand the mold to fill the disc space. A first injection condition triggers a second operating parameter, which maintains adequate pressure for a certain dwell time to completely fill the disc space and to distract the intervertebral disc space. Following the dwell time, a third operating parameter optionally permits a portion of the flowable biomaterial to be expelled from the intervertebral disc space, followed by a second dwell time that continues until the biomaterial adequately cures.
The present method optionally includes pretreating the flowable biomaterial. The biomaterial can also be exposed to ultraviolet light, heating and/or mixed prior to delivery to the intervertebral disc space.
In one embodiment, the flow of biomaterial is directed away from the intervertebral disc space until a predetermined quantity of biomaterial is delivered to a chamber in a purge device. In one embodiment, the first operating parameter includes the step of applying a first operating pressure to the flowable biomaterial in the reservoir and applying a second operating pressure, lower than the first operating pressure, to the flowable biomaterial in the reservoir. In another embodiment the intervertebral disc space exerts a pressure on the flowable biomaterial in the intervertebral disc space greater than the second operating pressure.
The step of monitoring at least one injection condition typically includes monitoring the pressure of the flowable biomaterial between the reservoir and the intervertebral disc space and/or the pressure of the flowable biomaterial in the intervertebral disc space. The step of monitoring at least one injection condition can be monitoring at least one of the pressure, the flow rate, elapsed time, or the total volume of the flowable biomaterial flowing between the reservoir and the intervertebral disc space.
The present method also includes the step of recording data corresponding to at least one of the injection conditions during the flow of flowable biomaterial. The injection condition data is optionally uploaded to a computer. The present method also includes determining whether any of the injection conditions is in an out of specification condition and indicating an out of specification condition. Alternatively, the flow of biomaterial is altered and/or the biomaterial is withdrawn from the intervertebral disc space in response to an out of specification condition.
The flow of flowable biomaterial can be manually switched to the second operating parameter in response to one or more of the injection conditions reaching a threshold level or automatically switched by a controller. The present method optionally includes adjusting the threshold level as a function of patient parameters. The first and second operating parameter typically comprises a plurality of variables, such as for example, injection pressure, biomaterial temperature, and the like.
The present method also includes positioning an evaluation mold in the intervertebral disc space prior to the delivery of the biomaterial. A liquid is delivered to the evaluation mold so that the mold substantially fills the intervertebral disc space and measurements, such as for example disc height, pressure, and the like, are taken. The liquid is removed from the evaluation mold and the volume of liquid injected and/or removed is measured. The evaluation mold is then removed from the intervertebral disc space. The liquid is preferably delivered under pressure sufficient to distract the intervertebral disc space. The liquid and/or the evaluation mold optionally have radiopaque properties. The present invention also includes use of the present biomaterial injection system to control delivery and/or removal of the liquid to the evaluation mold.
In the preferred embodiment, imaging can be used to measure the distraction of the intervertebral disc space, to evaluate whether the mold substantially fills the intervertebral disc space, to evaluate the geometry of the intervertebral disc space, and/or to supply information to the surgeon regarding adequacy of the nucleus removal. The evaluation mold can either be positioned in the implant mold, directly in the annulus, or within the disc space in the case of complete disc removal. In another embodiment, the intervertebral disc space containing the evaluation mold and the liquid is imaged and at least one of the first operating parameter and/or the second operating parameter are established based on the imaging of the intervertebral disc space. In one embodiment, the intervertebral disc space is imaged to estimate the volume of biomaterial required. That estimate can then be compared to the amount of liquid removed from the evaluation mold.
In another embodiment, a liquid is delivered under pressure to the evaluation mold sufficient to distract the intervertebral disc space. The volume of liquid in the evaluation mold may be held constant for a period of time. Additional liquid is added to the evaluation mold when the pressure in the mold drops to a predetermined level. The steps of delivering, holding and adding additional liquid is preferably repeated a plurality of cycles.
In another embodiment, a liquid is continuously delivered to the evaluation mold at a constant pressure. The rate at which the liquid is delivered to the evaluation mold is measured. The compliance of the intervertebral disc space is measured as a function of the rate of change of the delivery of liquid.
The present method also includes positioning a guide wire in the mold and imaging the intervertebral disc space containing the guide wire. The guide wire optionally includes an imaging target.
The present method also includes positioning a radiopaque sheath over the mold before the delivery of the biomaterial. The intervertebral disc space containing the radiopaque sheath is imaged and the radiopaque sheath is removed before delivering the biomaterial.
The present invention is also directed to an apparatus adapted to deliver a flowable biomaterial to an intervertebral disc space. The apparatus includes a reservoir containing the flowable biomaterial fluidly coupled to the intervertebral disc space, at least one sensor adapted to monitor at least one injection condition of the flowable biomaterial, and a controller. The controller is programmed to monitor the at least one sensor and to control the flow of the flowable biomaterial into the mold in accordance with a first operating parameter. In response to one or more of the injection conditions reaching a threshold level, the controller controls the flow of the flowable biomaterial in accordance with a second operating parameter and maintains the second operating parameter during a certain time period or dwell time before switching to the third operating parameter and maintaining the third operating parameter during at least a portion of the curing of the flowable biomaterial.
In one embodiment, the apparatus includes a mold located in the intervertebral disc space fluidly coupled to the reservoir containing the flowable biomaterial. The controller is programmed so that the first operating parameter delivers the flowable biomaterial to the mold so that the mold substantially fills the intervertebral disc space.
In one embodiment, the controller is programmed to initiate a second operating parameter during which the system waits a predetermined period of time after the first operating parameter (i.e., the at least one injection condition reaches the threshold level at a second operating parameter) before initiating the third operating parameter. In another embodiment, the controller is programmed to deliver the flowable biomaterial in accordance with a third operating parameter that maintains the flowable biomaterial at a predetermined pressure in the intervertebral disc space for a predetermined period of time after the at least one injection condition reaches the threshold level and before the second operating parameter. Operating parameters can be linear, non-linear, continuous, discontinuous, or any other configuration necessary to achieve the desired injection profile. The operating parameter can also be modified real-time based on feedback from the sensors monitoring the injection conditions.
The controller is preferably programmed so that the first operating parameter comprises a pressure sufficient to distract the intervertebral disc space. In another embodiment, the controller is programmed so that the second operating parameter permits a portion of the flowable biomaterial to be expelled from the intervertebral disc space. The controller is also optionally programmed to control pretreatment of the flowable biomaterial.
The apparatus optionally includes a source of ultraviolet light and/or heating directed at the flowable biomaterial prior to delivery to the intervertebral disc space. The present apparatus also optionally includes a mixing device located between the reservoir of flowable biomaterial and the intervertebral disc space. The present apparatus also optionally includes a purging device adapted to direct a predetermined quantity of the flow of biomaterial away from the intervertebral disc space.
In one embodiment, the controller is programmed so that the second operating parameter applies a second operating pressure to the biomaterial in the reservoir that is lower than the first operating pressure applied under the first operating parameter. The controller can monitor the pressure of the flowable biomaterial between the reservoir and the intervertebral disc space and or in the intervertebral disc space. The controller is preferably programmed to monitor at least one injection condition comprises monitoring at least one of the pressure, the flow rate, elapsed time, or the total volume of the flowable biomaterial flowing between the reservoir and the intervertebral disc space.
The controller is preferably programmed to record data corresponding to at least one of the injection conditions during the flow of flowable biomaterial. In one embodiment, the controller is programmed to upload to a computer data corresponding to at least one of the injection conditions recorded during the flow of flowable biomaterial.
The controller may also be programmed to determine whether the at least one injection condition comprises an out of specification condition and to indicate an out of specification condition. Alternatively, the controller is programmed to alter the flow of flowable biomaterial or to withdraw at least a portion of the biomaterial from the intervertebral disc space in response to an out of specification condition.
The controller preferably adjusts the threshold level as a function of patient parameters. The first, second and third operating parameters typically comprises a plurality of variable.
The present invention may also include an evaluation mold adapted to be positioned in the intervertebral disc space prior to the delivery of the biomaterial and a liquid adapted to be delivered to the evaluation mold so that the mold substantially fills the intervertebral disc space. The controller is preferably programmed to remove the liquid from the evaluation mold and to measure the amount of liquid removed from the evaluation mold. The liquid and/or the evaluation mold optionally have radiopaque properties.
In one embodiment, the controller is programmed to estimate the volume of biomaterial required to fill the intervertebral disc space and to compare the amount of liquid removed from the evaluation mold with an estimated volume of the intervertebral disc space measured using imaging techniques.
In another embodiment, the controller is programmed to deliver a liquid under pressure to the evaluation mold sufficient to distract the intervertebral disc space, to hold the volume of liquid in the evaluation mold constant for a period of time, and to add additional liquid to the evaluation mold when the pressure in the mold drops to a predetermined level. The controller is preferably programmed to repeat the steps a plurality of cycles and estimate the compliance of the intervertebral disc space or spinal unit. In one embodiment, the operating parameters are modified in response to the estimate of compliance.
In another embodiment, the controller is programmed to continuously deliver a liquid to the evaluation mold at a constant pressure, to measure the rate at which the iiquid is delivered to the evaluation mold, and to estimate the compliance of the intervertebral disc space as a function of the changing rate at which the liquid is delivered.
In one embodiment, the present invention includes a guide wire positioned in the mold. In another embodiment, a radiopaque sheath is positioned over the mold.
The present invention is also directed to a controller programmed to determine whether at least one injection condition comprises an out of specification condition and to generate a signal of the out of specification condition.
The present invention is also directed to an apparatus adapted to deliver a flowable biomaterial to a mold located in an intervertebral disc space. The apparatus includes a reservoir containing the flowable biomaterial fluidly coupled to the mold, an actuator providing a flow of the flowable biomaterial into the mold in accordance with a first operating parameter and at least one sensor monitoring at least one operating parameter of the flowable biomaterial. The apparatus also includes a display adapted to indicate that the at least one injection condition has reached a threshold level and a switch that controls the flow the flowable biomaterial in accordance with a second operating parameter.
As used herein the following words and terms shall have the meanings ascribed below:
“biomaterial” will generally refer to a material that is capable of being introduced to the site of a joint and cured to provide desired physical-chemical properties in vivo. In one embodiment the term will refer to a material that is capable of being introduced. to a site within the body using minimally invasive mechanism, and cured or otherwise modified in order to cause it to be retained in a desired position and configuration. Generally such biomaterials are flowable in their uncured form, meaning they are of sufficient viscosity to allow their delivery through a delivery tube of on the order of about 1 mm to about 6 mm inner diameter, and preferably of about 2 mm to about 3 mm inner diameter. Such biomaterials are also curable, meaning that they can be cured or otherwise modified, in situ, at the tissue site, in order to undergo a phase or chemical change sufficient to retain a desired position and configuration;
“cure” and inflections thereof, will generally refer to any chemical transformation (e.g., reacting or cross-linking), physical transformation (e.g., hardening or setting), and/or mechanical transformation (e.g., drying or evaporating) that allows the biomaterial to change or progress from a first physical state or form (generally liquid or flowable) that allows it to be delivered to the site, into a more permanent second physical state or form (generally solid) for final use in vivo. When used with regard to the method of the invention, for instance, “curable” can refer to uncured biomaterial, having the potential to be cured in vivo (as by catalysis or the application of a suitable energy source), as well as to the biomaterial in the process of curing. As further described herein, in selected embodiments the cure of a biomaterial can generally be considered to include three stages, including (a) the onset of gelation, (b) a period in which gelation occurs and the biomaterial becomes sufficiently tack-free to permit shaping, and (c) complete cure to the point where the biomaterial has been finally shaped for its intended use.
“minimally invasive mechanism” refers to a surgical mechanism, such as microsurgical, percutaneous, or endoscopic or arthroscopic surgical mechanism, that can be accomplished with minimal disruption of the pertinent musculature, for instance, without the need for open access to the tissue injury site or through minimal incisions (e.g., incisions of less than about 4 cm and preferably less than about 2 cm). Such surgical mechanism are typically accomplished by the use of visualization such as fiberoptic or microscopic visualization, and provide a post-operative recovery time that is substantially less than the recovery time that accompanies the corresponding open surgical approach;
“mold” will generally refer to the portion or portions of an apparatus of the invention used to receive, constrain, shape and/or retain a flowable biomaterial in the course of delivering and curing the biomaterial in situ. A mold may include or rely upon natural tissues (such as the annular shell of an intervertebral disc) for at least a portion of its structure, conformation or function. The mold, in turn, is responsible, at least in part, for determining the position and final dimensions of the cured prosthetic implant. As such, its dimensions and other physical characteristics can be predetermined to provide an optimal combination of such properties as the ability to be delivered to a site using minimally invasive mechanism, filled with biomaterial, prevent moisture contact, and optionally, then remain in place as or at the interface between cured biomaterial and natural tissue. In one embodiment the mold material can itself become integral to the body of the cured biomaterial. The mold can be elastic or inelastic, permanent or bio-reabsorbable.
Intervertebral disc space refers generally to the space between adjacent vertebrae. The embodiments illustrated herein are equally applicable to both a complete disc replacement and to a full or partial nucleus replacement. A replacement disc refers to both a complete disc replacement and to a full or partial nucleus replacement.
The reservoir 3 is adapted to hold the biomaterial 23, and in some embodiments, the reservoir 3 heats and/or mixes the biomaterial 23. In some embodiments, the biomaterial 23 is pretreated before use. The biomaterial 23 can either be pretreated before being placed in the reservoir 3 or the pretreatment can be performed in the reservoir 3. For example, the biomaterial 23 can be heated, mechanically agitated, or both, such as heating in a rotating oven before being placed in the reservoir 3. For some polyurethane biomaterials, for example, sealed packages of biomaterial 23 are heated while rotating in an oven at about 75° C. for about 3 hours, maintained at 75° C. degrees C. without rotating for an additional 3 hours, and then kept in the oven at about 37° C. until surgical implantation. During the second 3 hour period, the package of biomaterial 23 is preferably retained in the oven without rotating and in an upright position during heating so that bubbles rise to the top. The flowable biomaterial 23 containing the bubbles is preferably purged before it reaches the mold, as will be discussed below.
A chamber 5 is optionally located in-line between the reservoir 3 and the mold 13. The chamber 5 can be used to heat, mix and/or stage the biomaterial 23. In some embodiments, the chamber 5 can be used to initiate curing of the biomaterial 23, such as for example by exposing the biomaterial 23 to an ultraviolet light source or a heat source 5 b.
An actuator 21 is mechanically coupled to the reservoir to expel the biomaterial 23 from the reservoir 3 and into the delivery tube 11. The actuator 21 can be a pneumatic or hydraulic cylinder, a mechanical drive such as an electric motor with a ball screw, a drive screw or belt, or a variety of other mechanisms well know to those of skill in the art. Control of the actuator 21 is typically the primary operating parameter used to create the desired injection profile. Other possible operating parameters that can be controlled by the controller 15 include releasing biomaterial 23 through one or more of the purge devices 7 a, 7 b, biomaterial temperature, biomaterial viscosity, and the like.
As used herein, “operating parameter” refers to one or more independent variables that can be controlled during the injection of biomaterial. The operating parameters can be linear, non-linear, continuous, discontinuous, or any other configuration necessary to achieve the desired injection profile. The operating parameter can also be modified real-time based on feedback from the sensors monitoring the injection conditions. For example, a control algorithm, such as Proportional Integral Derivative (PID) control, can be used to evaluate the injection condition data in light of the desired injection profile.
For embodiments where the actuator 21 is a pneumatic cylinder, it should be noted that many hospitals and clinics do not have sources of compressed air greater than 50 pounds per square inch (hereinafter “psi”). Thus, in some embodiments the pneumatic cylinder needs to magnify the available compressed air source by a factor of about 3. Thus, an initial pressure of about 50 psi becomes about 150 psi in the reservoir 3.
The delivery tube 11 preferably includes at least one purge device 7 a. In the illustrated embodiment, the purge device 7 a is located downstream of the chamber 5. In another embodiment, a secondary purge device 7 b is located closer to the mold 13. The purge devices 7 a and 7 b are referred to collectively as “7”. Suitable purge devices can include but are not limited to, reservoirs, three-way valve systems, and the like. The purge devices 7 can divert or redirect the flow of biomaterial 23 aside in order to purge a portion, which can include an initial portion that may be inadequately mixed or contain bubbles. The purge devices 7 can also be employed if there is a system failure, such as rupture of a mold 13, to quickly divert biomaterial from the intervertebral disc space.
The purge devices 7 a, 7 b can be operated manually or automatically. In the preferred embodiment one or both are operated by controller 15 and/or using the mechanism in
In the illustrated embodiment, the biomaterial injection system 1 preferably includes one or more sensors 9 a, 9 b, 9 c, 9 d, 9 e, 9 f, 9 g and 9 h (referred to collectively as “9”) located at strategic locations in the present biomaterial injection system 1. In the illustrated embodiment, sensor 9 a is located between the reservoir 3 and the chamber 5. Sensor 9 b is located between the chamber 5 and the purge device 7 a. Another sensor 9 c is located downstream of the purge device 7 a. Sensor 9 d is located close to the mold 13. In the preferred embodiment, the sensor 9 d is located as close to the mold 13 as possible. The pressure sensor 9 g is located substantially in the mold 13. The sensor 9 h is optionally located in the intervertebral disc space 19, but outside the mold 13. The sensor 9 e is located in the reservoir 3 and the sensor 9 f is located in the actuator 21.
Each of the individual sensors 9 can measure any one of a plurality of injection conditions, such as for example biomaterial color, biomaterial viscosity, pressure, quantity and/or size of air bubbles in the biomaterial, flow rate, temperature, total volume, duration of the flow of the biomaterial 23, or any other injection condition that characterizes a proper injection profile. As used herein, “injection condition” refers to one or more dependent variables that are effected by one or more operating parameters. An “injection profile” refers to values of one or more injection conditions evaluated over time. An exemplary injection profile is illustrated in
Output from the sensors 9 is preferably delivered to controller 15. The controller 15 preferably attaches a time/date stamp to all injection condition data. Not all of the sensors 9 necessarily perform the same function. For example, the sensors 9 a and 9 d may monitor pressure, while the sensor 9 b monitors temperature and the sensor 9 c monitors flow.
The sensors 9 can be in-line with the delivery tube 11, fluidly coupled to the delivery tube 11, coupled to the delivery tube 11 by a diaphragm, or engaged with the delivery tube using a variety of other techniques. The sensors 9 may be disposable or reusable. A suitable pressure sensor 9 can include any device or system adapted to measure or indicate fluid pressure within a surgical fluid system and adapted for attachment to a delivery mechanism 11. Examples of suitable pressure sensors include, but are not limited to, those involving a suitable combination of pressure gauge, electronic pressure transducer and/or force transducer components. Such components that can be adapted to permit the accurate and substantially real time measurement of pressure in a remote fluid, by shunting a sample of such fluid, can also be used particularly where the fluid is itself undergoing a change in properties in the course of its ongoing cure.
The various components of the biomaterial injection system 1 are preferably fabricated from polymeric or other materials that provide an optimal combination of properties such as compatibility with the biomaterial 23 and the ability to be sterilized and/or to be disposable.
Operation of the actuator 21 is preferably monitored and/or directed by the controller 15. Output from the sensors 9 is preferably delivered to the controller 15 to create a closed-loop feed back system. The controller 15 preferably includes a processor and a memory device. The controller 15 can be a special purpose computer, a general purpose computer such as a personal computer, independent signal conditioning circuits, threshold comparator circuits and switch circuits. In some embodiments, the controller 15 is a user interface to effect manual control of the system 1.
The controller 15 preferably includes one or more displays 16 that communicate injection conditions to the surgical staff. The controller 15 can also provide audio indications of the injection condition data shown on the displays 16. In another embodiment, the surgical staff manually overrides the operation of the controller 15 so as to permit one or more operating parameters to be controlled manually based on data obtained from the displays 16.
As illustrated in
The mixing of the two or more components 23 a, 23 b of the biomaterial 23 can initiate a chemical curing reaction. Although the reservoir of
Alternatively, the biomaterial may be a single component system that can be located in one or more of the compartments 37 a, 37 b. Single component biomaterials can be cured using, for example, ultraviolet light, ultrasonic energy, or heat. In one embodiment, the chamber 5 can optionally include an ultraviolet light source, a heater, or any other device or source of energy that initiates the curing process of the biomaterial 23.
As biomaterial is delivered to the inlet 72 under pressure, it is advanced through the passageway 78 into the chamber 76. The volume of the chamber 76 is designed to accommodate the optimum amount of biomaterial 23 that is typically purged prior to delivery to the mold 13. Once the chamber 76 is filled with biomaterial 23, force 88 is applied to the piston 80. As the piston 80 is driven toward surface 90 on housing 92 by the pressure of the biomaterial 23, connecting member 94 displaces the valve 82 along with the piston 80. Vent hole 81 allows air to escape from behind the piston 80 as it advances in the housing 92.
In another embodiment, the delivery tube 11 is sized to fit the inlet 26 formed in the annulus 25 snuggly to allow the biomaterial 23 to be delivered under pressure without leaking. In the embodiment of
As discussed above, the controller 15 preferably monitors and records the injection condition data and attaches a time/date stamp.
By linking the historic injection profiles 20 with the patient's pre-surgical and post-surgical patient parameters, a database is created that can be searched by surgeons for the injection profile 20 that most closely matches the current patient's parameters. Once the optimum profile is selected, it can optionally be downloaded to the controller 15 prior to performing the present method.
Preliminary Analysis of the Patient
The optimum injection profile and the corresponding injection conditions may vary as a function of patient parameters, such as for example, the patient's weight, age, gender, disc height, disc degeneration index, disc compliance, general clinical goals, patient-specific clinical goals, and the like. For example, a diseased disc may require a higher injection pressure and a higher termination pressure to restore more disc height and a longer dwell time at the threshold and/or termination pressure. Alternatively, if a bone scan indicates reduced bone density or that the vertebral bodies are otherwise compromised, a lower injection pressure may be indicated. The present invention includes creating an injection profile as a function of patient parameters and clinical goals. In some embodiments, a custom injection profile is created for each patient.
One mechanism for selecting the appropriate injection profile for the patient is to conduct an analysis on the annulus 25. Imaging or palpitation of the annulus, preferably after nuclectomy, is optionally performed before the delivery of the biomaterial to assess annular integrity. In one embodiment, an instrument is used that applies a known force to the annular wall 25 and measures the amount of deflection. In one embodiment, an evaluation mold 13′ (which may be the same mold or a different mold than the implant mold 13), is inserted into the patient's annulus 25 after the nuclectomy is completed, such as illustrated in
In some embodiments, the evaluation mold 13′ and/or the delivery tube 11 have radiopaque properties. The radiopaque properties can be provided by constructing the evaluation mold 13′ and/or the delivery tube 11 from a radiopaque material or including radiopaque markings, such as inks, particles, beads, and the like on the evaluation mold 13′ and/or the delivery tube 11 to facilitate imaging. An image, such as an x-ray, MRI, CAT-scan, or ultrasound, is then taken of the patient's intervertebral disc space 19 to check if the nuclectomy (i.e., the cavity 24) is symmetrical, of adequate size, of the desired geometry and/or if the required amount of distraction has been achieved. This information is used by the surgeon to decide when the proper amount of nucleus material has been removed from the annulus 25.
The volume of contrast medium necessary to fill the cavity 24 and to achieve the desired amount of distraction, as verified by the image sequence, provides an indication of the volume of biomaterial 23 necessary for the procedure. In another embodiment, imaging is used to estimate the amount of nucleus that needs to be removed. The volume of liquid necessary to fill the evaluation mold 13′ is then compared to the estimated volume measured using imaging techniques and a determination is made whether additional nucleus material should be removed.
In another embodiment illustrated in
The contrast medium 102 is preferably delivered at a pressure sufficient to fully expand the mold 13 into the cavity 24. The evaluation mold 13′ also serves to position the mold 13 within the annulus 25. As best illustrated in
As illustrated in
The evaluation mold 13′ can also be used to measure the compliance of the annulus 25. For example, the evaluation mold 13′ can be pressurized with a fixed volume of saline or a liquid contrast medium to the level anticipated during delivery of the biomaterial. Images of the intervertebral disc space 19 are optionally taken at various pressures to measure the distraction of the adjacent vertebrate 17. After a period of time, such as about three to about five minutes, the tissue surrounding the intervertebral disc space 19 generally relaxes, causing the pressure measured in the evaluation mold 13′ to drop. Additional saline or contrast medium is then introduced into the evaluation mold 13′ to increase the pressure in the intervertebral disc space 19 to the prior level. The tissue surrounding the intervertebral disc space 19 again relaxes as measured by the reduction in pressure within the evaluation mold 13′. By repeating this procedure several times, the surgeon can assess the compliance of the intervertebral disc space 19 and/or the annulus 25, and the likely volume of biomaterial 23 necessary for the procedure.
In another embodiment, compliance is measured by continuously adding a liquid to the evaluation mold 13′ at a rate sufficient to maintain a generally constant pressure in the biomaterial delivery system 1 and/or in the intervertebral disc space. The change in the rate at which liquid needs to be added to maintain a constant pressure provides information that can be used to estimate compliance of the annulus 25 and/or the intervertebral disc space 19.
A healthy, compliant annulus can typically handle several pressurization/relaxation cycles. A diseased annulus 25 may show less relaxation (e.g., less compliance) after being pressurized. Depending upon the status of the annulus 25 and the intervertebral disc space 19, a patient-appropriate injection profile can be selected.
This compliance evaluation can be either controlled manually or by the controller 15. The compliance data collected can be used to determine the operating parameters to produce the injection profile best suited to the patient.
The present biomaterial delivery system 1 permits one or more operating parameters to be controlled to achieve the desired injection conditions. The injection conditions are monitored, recorded and controlled real-time. The injection conditions may include, for example, biomaterial temperature and viscosity, biomaterial flow rate, biomaterial pressure, volume of biomaterial, distraction pressure, total distraction, and time, such as for example distraction time. These injection conditions can vary over the course of the medical procedure, so a plurality of injection conditions are preferably monitored and recorded as a function of time. The injection conditions can also be evaluated as a function of any of the other injection conditions, such as for example, pressure as a function of volume or flow. In the present invention, the pressure in the mold 13 is one possible injection condition for determining when to terminate the flow of biomaterial 23. Alternatively, the volume of biomaterial 23 delivered to the mold 13 can also be used for this purpose.
Once an optimum injection profile for the patient is determined (see e.g.,
The injection conditions can be used to signal that the procedure is out of specification. Alternatively, the controller 15 can calculate trends or slopes of the injection conditions to predict whether a particular injection condition will likely be out of specification. As used herein, “out of specification” refers to one or more injection conditions that have deviated from the desired injection profile and/or are exhibiting a trend that indicates a future deviation from the injection profile.
In those situations where the injection conditions can not be brought under control, such as for example if the mold 13 malfunctions, the procedure is aborted and the biomaterial 23 is preferably withdrawn from the patient before it cures. As used herein, malfunction refers to ruptures, fractures, punctures, deformities, kinks, bends, or any other defect that results in more or less biomaterial being injected into the patient than would otherwise occur if the mold was operating as intended. Alternatively, if the malfunction occurs in a location other than the mold, such as in the delivery tube 11 or if the mold kinks and can not be deployed and expanded to fill the intervertebral disc space, or if the vacuum tube 11′ is obstructed an air in the mold 13 can not be evacuated, less biomaterial will be injected into the mold than is desired.
The controller 15 monitors one or more sensors 9 to determine if the injection conditions are under control. If any one or a combination of the injection conditions are out of specification, a number of corrective actions can be taken. If the deviation from the preferred injection profile is minor, the controller 15 can attempt a correction. During a given medical procedure where the resistance to the flow of biomaterial 23 is essentially fixed, the primary mechanisms for controlling the injection conditions are 1) decreasing, increasing or reversing the drive pressure exerted on the reservoir 3 by the actuator 21; 2) releasing biomaterial 23 through one or more of the purge devices 7 a, 7 b; and 3) changing the temperature, and hence the viscosity, of the biomaterial 23.
If the deviation is above a particular threshold, the controller 15 may signal the surgical staff. Alternatively, the surgical staff can monitor the displays 16 for any out of specification injection conditions. The displays 16 preferably highlight the injection condition(s) that have deviated from the preferred injection profile. In those instances where an injection condition is seriously out of specification, the controller 15 will signal that the procedure should be aborted and/or automatically abort the procedure. Typically, the actuator 21 will decrease or reverse the drive pressure on the reservoir 3 in anticipation of aborting the procedure. If the procedure is aborted, any biomaterial 23 in the mold 13 and/or the intervertebral space 19 is removed, either through the purge device 7 b or manually by the surgeon. The mold 13 is also removed.
At the beginning of time sequence 81, the biomaterial 23 is immediately upstream of the purge device 7 a. During time sequence 81, the biomaterial 23 begins to enter the purge device 7 a. During time sequence 82, the biomaterial 23 is filling the purge device. The flow rate 72 is relatively constant and the total volume 76 of biomaterial continues to increase. The sudden increase of injection pressure 74 between the end of time sequence 81 and the beginning of time sequence 82 is the result of internal resistance to the flow of biomaterial 23 at the purge device 7 a.
At time sequence 83, the purge device 7 a switches the flow of biomaterial 23 to the delivery tube 11, resulting in a rapid spike in injection pressure 74. At time sequence 84, the biomaterial 23 fills the delivery tube 11. Injection pressure 74 increases due to resistance to the flow of biomaterial 23 through the delivery tube 11. At time sequence 91, the biomaterial 23 reaches the folded mold 13, resulting in a rapid increase in injection pressure 74 as the mold unfolds.
At time sequence 85 the biomaterial 23 begins to fill the mold 13. The slight drop in injection pressure 74 is the result of the biomaterial 23 flowing freely into the mold 13. The expanding mold 13 hits the inner wall of the annulus at time sequence 86. The flow rate 72 continues to drop and the total volume 76 of biomaterial 23 continues to increase at a generally constant rate. At time sequence 87, the injection pressure 74 of the biomaterial 23 continues to increase at a different rate as it displaces the vertebrae 17 and distracts the intervertebral disc space 19. The muscles and tendons attached to the vertebrate 17 are stretched elastically by the injection pressure 74 of the biomaterial 23 in the mold 13.
At time sequence 88, the threshold injection pressure 74 is reached. Time sequence 88 represents the maximum distraction of the intervertebral disc space 19. In the illustrated example, the drive pressure exerted by the actuator 21 on the reservoir 3 during time sequences 81 through 88 is generally constant. Once the injection pressure 74 at time sequence 88 is reached, a transition is triggered where the drive pressure at the actuator 21 is reduced from a first operating parameter to a second operating parameter. As a result, the injection pressure 74 is reduced. The flow rate 72 is about zero and the total volume 76 of biomaterial is at a maximum.
In another embodiment, once the injection pressure 74 at time sequence 88 is reached, a transition is triggered from a first operating parameter to a second operating parameter where the drive pressure at the actuator 21 is held constant for some period of time, such as for example 3-120 seconds. At the end of the dwell time, the drive pressure is reduced from the second operating parameter to a third operating parameter. Again, the injection pressure 74 is reduced and the flow rate 72 is about zero and the total volume 76 of biomaterial is at its final volume.
At time sequence 89 the drive pressure exerted on the biomaterial 23 in the reservoir 3 by the actuator 21 is reduced. This reduction can alternatively be achieved by releasing a portion of the biomaterial 23 through a purge device 7 a, 7 b. The pressure created in the intervertebral disc space 19 acting on the mold 3 is now greater than the injection pressure 74 of the biomaterial 23 in the biomaterial delivery system 1. Consequently, tension of the muscles and tendons surrounding the vertebrate 17 provides a compressive force that results in a flow of biomaterial 23 out of the mold 13, as indicated by the negative flow rate 72 during time sequence 89 and a decrease in total volume 93.
At time sequence 90 the injection pressure 74 of the biomaterial 23 is generally constant. The pressure exerted by the mold 13 and biomaterial 23 is nearly in balance with the pressure exerted by the vertebrate 17 on the mold 13. The flow rate 72 and the change in total volume 76 are both about zero. With the system 1 now in stasis, the biomaterial 23 begins to cure. Once the biomaterial 23 is at least partially cured, the delivery tube 11 is removed.
In these embodiment, the biomaterial injection system 1 initially operates at a first operating parameter. When one of the injection conditions reaches a threshold level, such as for example a threshold pressure as measured in the mold 13, the controller 15 switches or transitions to second operating parameter. In an alternate embodiment, the threshold trigger could be flow rate, time, volume or temperature of the biomaterial. In the embodiment of
In another embodiment, the second operating parameter is a dwell cycle where the pressure is maintained as some predetermined level for a predetermined period of time. At the end of the dwell cycle, the controller switches to a third operating parameter, which includes reducing the pressure applied by the actuator 21 on the biomaterial 23 in the reservoir 3.
The relatively high injection pressure provides a number of benefits, including rapid filling of the mold 13 to reduce the chance of leaving voids or under-filled regions. The biomaterial injection system 1 continues to operate at the first operating parameter until one of the injection conditions reaches a threshold level that triggers use of the second operating parameter.
The injection pressure used to determine a suitable threshold typically corresponds to the distraction pressure brought about by the delivery of biomaterial 23 within the disc space 19. The injection condition in this instance is the injection pressure measured at the sensors 9 c or 9 d, such as for example about 80 psi to about 150 psi. In one embodiment, the injection pressure triggers the controller 15 to transition to the second operation condition. In another embodiment, the second operating condition holds the injection pressure at a predetermined level for a predetermined dwell time.
It is possible to measure the pressures discussed above using any of the sensors 9 a-9 d and 9 g-9 h. Doing so would require calibrating the biomaterial injection system 1 so that a measured pressure at one of the sensors 9 is correlated to the actual pressure in the intervertebral disc space 19, such as measured by sensor 9 g or 9 h. The factors required for such a calibration include the size of the mold 13, the resistance to fluid flow between the reservoir 3 and the mold 13, the flow rate, the viscosity and temperature of the biomaterial 23, the cure time of the biomaterial, and a variety of other factors. For example, with regard to mold size, the transition from the first operating parameter to the second operating parameter occurs when the injection conditions measured at the sensor 9 b is about 100 psi to about 125 psi for a mold 13 with a volume of about 1.8 cubic centimeters; about 105 psi to about 130 psi for a mold 13 with a volume of about 2.7 cubic centimeters; and about 110 psi to about 135 psi for a mold with a volume of about 4.0 cubic centimeters.
Initially, the pneumatic actuator 21 is supplied with compressed air through the first pressure regulator 53. When one or more of the sensors 9 a-9 d detects a threshold pressure, the pressure control switch 51 selects compressed air from the second pressure regulator 55 to drive the pneumatic actuator 21. In one embodiment, the directional control valve 49 is a normally open, four-way valve such as those available under the trade name of Four-Way Valve (SV271) available from Omega Engineering, Inc. Stamford, Conn.
In a related embodiment, the mold, or a kit that contains or is adapted for use with such a mold, can include tools adapted to position the mold 13 in situ. In one embodiment, the tool is a guide wire, such as for example the guide wire shown in
Optionally, and in order to facilitate the placement of the collapsed mold 13 within a sheath, the invention further provides a rod, e.g., a plastic core material or a metal wire, dimensioned to be placed within the mold 13, preferably by extending the rod through the conduit. Once in place, a vacuum can be drawn on the mold 13 through the air passageway in order to collapse the mold 13 around the rod. Simultaneously, the mold 13 can also be twisted or otherwise positioned into a desired conformation to facilitate a particular desired unfolding pattern when later inflated or filled with biomaterial. Provided the user has, or is provided with, a suitable vacuum source, the step of collapsing the mold 13 in this manner can be accomplished at any suitable time, including just prior to use.
In certain embodiments it will be desirable to collapse the mold 13 just prior to its use, e.g., when using mold materials that may tend to stick together or lose structural integrity over the course of extended storage in a collapsed form. Alternatively, such mold materials can be provided with a suitable surface coating, e.g., a covalently or noncovalently bound polymeric coating, in order to improve the lubricity of the surface and thereby minimize the chance that contacting mold surfaces will adhere to each other. In another embodiment, the outer surface of the mold 13 can be coated with a material that bonds to the inner surface of the cavity 24 in the annulus 25.
The method of the present invention can be used with any suitable curable biomaterial such as a curable polyurethane composition having a plurality of parts capable of being aseptically processed or sterilized, stablely stored, and mixed at the time of use in order to provide a flowable composition and initiate cure, the parts including: (1) a quasi-prepolymer component comprising the reaction product of one or more polyols, and one or more diisocyanates, optionally, one or more hydrophobic additives, and (2) a curative component comprising one or more polyols, one or more chain extenders, one or more catalysts, and optionally, other ingredients such as an antioxidant, hydrophobic additive, dyes and radiopaque markers. Upon mixing, the biomaterial is sufficiently flowable to permit it to be delivered to the body and fully cured under physiological conditions. A suitable biomaterial also includes component parts that are themselves flowable at injection temperature, or can be rendered flowable, in order to facilitate their mixing and use. Additional discussion of suitable biomaterials can be found in U.S. patent application Ser. Nos. 10/365,868 and 10/365,842, previously incorporated by reference.
The biomaterial used in this invention can also include polyurethane prepolymer components that react in situ to form a solid polyurethane (“PU”). The formed PU, in turn, includes both hard and soft segments. The hard segments are typically comprised of stiffer oligourethane units formed from diisocyanate and chain extender, while the soft segments are typically comprised of more flexible polyol units. These two types of segments will generally phase separate to form hard and soft segment domains because these segments tend to be thermodynamically incompatible with one another.
Those skilled in the relevant art, given the present teaching, will appreciate the manner in which the relative amounts of the hard and soft segments in the formed polyurethane, as well as the degree of phase segregation, can have a significant impact on the final physical and mechanical properties of the polymer. Those skilled in the art will therefore further appreciate the manner in which such polymer compositions can be manipulated to produce cured and curing polymers with a desired combination of properties within the scope of this invention. In some embodiments of the present invention, for instance, the hard segment in the formed PU ranges from about 20% to about 50% by weight and more preferably from about 20% to about 30% by weight and the soft segment from about 50% to about 80% and more preferably from about 70% to about 80% by weight, based on the total composition of the formed PU. Other embodiments may be outside of these ranges.
The biomaterial typically includes a plurality of component parts and employs one or more catalysts. The component parts, including catalyst, can be mixed to initiate cure, and then delivered, set and fully cured under conditions such as time and exotherm sufficient for its desired purpose. Upon the completion of cure, the resultant biomaterial provides an optimal combination of properties for use in repairing or replacing injured or damaged tissue. In a further embodiment, the biomaterial provides an optimal combination of properties such as compatibility and stability, in situ cure capability and characteristics (e.g., extractable levels, biocompatibility, thermal/mechanical properties), mechanical properties (e.g., tensile, tear and fatigue properties), and biostability.
Many mixing devices and methods have been used for biomaterials having a plurality of parts such as bone cement and tissue sealant. Mechanical mixing devices, such as the ones disclosed in U.S. Pat. No. 5,797,679 (Grulke, et al.) and U.S. Pat. No. 6,042,262 (Hajianpour), have been used for bone cement mixing. These mechanical mixing devices, however, can take a long time to get thorough mixing and can be difficult to operate in sterile field, especially for biomaterials having a plurality of parts with short cure time. On the other hand, some prior art two-part polyurethanes have a gel time of about 30 minutes. Without a proper seal method to seal off the delivery tube, a cure time of 30 minutes can be too long for operating room use.
It is important that mixing of the biomaterial occurs quickly and completely in the operating room in a sterile fashion. Biomaterial with induction times of less than 60 seconds and cure times of less than 5 minutes require a different mixing and delivery device than biomaterials of about 15 minutes of cure time. For biomaterial having two-part issocyanate-based polyurethane biomaterials, due to the sensitivity of NCO to OH ratio to the final properties of the cured biomaterial, there are several features that are important to the final properties of the in situ cured biomaterial. Several factors appear to have an impact on the in situ curable biomaterial mixing and delivery such as the number of mixing elements, purging of the initial volume from the static mixer and the effect of polymer flow during delivery using a static mixer.
The compatibility of the biomaterial can also be achieved by having more than the traditional two parts, e.g., three or more parts, and mixing them all together prior to polymer application. By storing the incompatible components in different cartridges and/or preconditioning each component according to individual requirements, it often can minimize the concern of component incompatibility. One example of a three-part biomaterial is to separate the polyol and chain extender in a two-part biomaterial.
In situ curability is largely dependent on the reaction rate, which can be measured by induction time and cure time. In general, fast cure (short induction time) will improve in situ curability by providing more complete polymerization, less leachable components, and better mechanical properties (e.g., less “cold layer” formed due to the cold surface of the implant). However, induction time should also be balanced with adequate working time needed for biomaterial injection, distraction, to provide enough time to access the injection conditions, identify if the injection conditions fall inside or outside an acceptable range, and if falling outside the acceptable range, halting or reversing the injection process.
Particularly for use in the disc, it has been determined that shorter induction times tend to provide improved biomaterial properties. For such uses, the induction time can be between about 5 and about 60 seconds, for instance, between about 5 and about 30 seconds, and between about 5 and about 15 seconds. By comparison, the total cure time for such biomaterial can be on the order of 5 minutes or less, 3 minutes or less, and one minute or less. In one embodiment of the present invention, however, the cure time can be on the order of about 15 minutes. In either case the cure time can be greater than 15 minutes by adjusting the amount of catalyst used.
The method of the present invention can be used for a variety of applications, including for instance, to provide a balloon-like mold for use preparing a solid or intact prosthesis, e.g., for use in articulating joint repair or replacement and intervertebral disc repair. Alternatively, the method can be used to provide a hollow mold, such as a sleeve-like tubular mold for use in preparing implanted passageways, e.g., in the form of catheters, such as stents, shunts, or grafts.
The present invention also provides a method and system for the repair of natural tissue that involves the delivery of biomaterial using minimally invasive mechanism, the composition being curable in situ in order to provide a permanent replacement for natural tissue. Optionally, the biomaterial is delivered to a mold that is positioned by minimally invasive mechanism and filled with biomaterial composition, which is then cured in order to retain the mold and cured composition in situ.
As can be seen, the annular shell can itself serve as a suitable mold for the delivery and curing of biomaterial. Optionally, the interior surface of the annular shell can be treated or covered with a suitable material in order to enhance its integrity and use as a mold. One or more inflatable devices, such as the molds described herein, can be used to provide molds for the delivery of biomaterial. The same inflatable devices used to distract the joint space can further function as molds for the delivery and curing of biomaterial.
The method of the present invention can also be used to repair other joints, including diarthroidal and amphiarthroidal joints. Examples of suitable diarthroidal joints include the ginglymus (a hinge joint, as in the interphalangeal joints and the joint between the humerus and the ulna); throchoides (a pivot joint, as in superior radio-ulnar articulation and atlanto-axial joint); condyloid (ovoid head with elliptical cavity, as in the wrist joint); reciprocal reception (saddle joint formed of convex and concave surfaces, as in the carpo-metacarpal joint of the thumb); enarthrosis (ball and socket joint, as in the hip and shoulder joints) and arthrodia (gliding joint, as in the carpal and tarsal articulations).
An illustration of the surgical use of one embodiment of the intervertebral prosthesis system of the invention is as follows
For embodiments that use multi-part biomaterials, the biomaterial components are forced by positive pressure out of the reservoir and through a static mixer. The initially inadequately mixed portion of the mixed biomaterial are preferably shunted through a purge device. Once the initial portion of the biomaterial has been shunted, the valve is redirected to permit the biomaterial to continue onward through the flow path and into the mold.
Patents and patent applications disclosed herein, including those cited in the Background of the Invention, are hereby incorporated by reference. Other embodiments of the invention are possible. It is to be understood that the above description is intended to be illustrative, and not restrictive. Many other embodiments will be apparent to those of skill in the art upon reviewing the above description. The scope of the invention should, therefore, be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US4834757 *||28 Mar 1988||30 May 1989||Brantigan John W||Prosthetic implant|
|US5047055 *||21 Dic 1990||10 Sep 1991||Pfizer Hospital Products Group, Inc.||Hydrogel intervertebral disc nucleus|
|US5342298 *||31 Jul 1992||30 Ago 1994||Advanced Cardiovascular Systems, Inc.||Automated fluid pressure control system|
|US5425772 *||20 Sep 1993||20 Jun 1995||Brantigan; John W.||Prosthetic implant for intervertebral spinal fusion|
|US5459700 *||22 Nov 1993||17 Oct 1995||Advanced Cardiovascular Systems, Inc.||Manual timer control for inflation device|
|US5460609 *||22 Nov 1993||24 Oct 1995||Advanced Cardiovascular Systems, Inc.||Electromechanical inflation/deflation system|
|US5556429 *||6 May 1994||17 Sep 1996||Advanced Bio Surfaces, Inc.||Joint resurfacing system|
|US5562614 *||22 Nov 1993||8 Oct 1996||Advanced Cardiovascular Systems, Inc.||Programmable manifold system for automatic fluid delivery|
|US5562621 *||22 Nov 1993||8 Oct 1996||Advanced Cardiovascular Systems, Inc.||Communication system for linking a medical device with a remote console|
|US5599301 *||22 Nov 1993||4 Feb 1997||Advanced Cardiovascular Systems, Inc.||Motor control system for an automatic catheter inflation system|
|US5704912 *||17 Mar 1995||6 Ene 1998||Advanced Cardiovascular Systems, Inc.||Syringe assembly mounting system for inflation control system|
|US5795353 *||2 Nov 1996||18 Ago 1998||Advanced Bio Surfaces, Inc.||Joint resurfacing system|
|US5797679 *||17 May 1996||25 Ago 1998||Stryker Corporation||Surgical cement mixer apparatus|
|US5827289 *||5 Jun 1996||27 Oct 1998||Reiley; Mark A.||Inflatable device for use in surgical protocols relating to treatment of fractured or diseased bones|
|US5888220 *||23 Ene 1996||30 Mar 1999||Advanced Bio Surfaces, Inc.||Articulating joint repair|
|US5951563 *||8 Oct 1998||14 Sep 1999||Brown; Byron L.||Sensor system for flowable cement|
|US6042262 *||16 Sep 1997||28 Mar 2000||Stryker Technologies Corportion||Apparatus for storing, mixing, and dispensing two-component bone cement|
|US6048346 *||13 Ago 1997||11 Abr 2000||Kyphon Inc.||Systems and methods for injecting flowable materials into bones|
|US6066154 *||22 Ene 1997||23 May 2000||Kyphon Inc.||Inflatable device for use in surgical protocol relating to fixation of bone|
|US6079868 *||2 Mar 1998||27 Jun 2000||Advanced Bio Surfaces, Inc.||Static mixer|
|US6140452 *||18 Nov 1998||31 Oct 2000||Advanced Bio Surfaces, Inc.||Biomaterial for in situ tissue repair|
|US6187048 *||23 May 1995||13 Feb 2001||Surgical Dynamics, Inc.||Intervertebral disc implant|
|US6224630 *||29 May 1998||1 May 2001||Advanced Bio Surfaces, Inc.||Implantable tissue repair device|
|US6240926 *||19 May 1999||5 Jun 2001||The Trustees Of The University Of Pennsylvania||Compositions and methods for intervertebral disc reformation|
|US6248131 *||5 Sep 1997||19 Jun 2001||Advanced Bio Surfaces, Inc.||Articulating joint repair|
|US6254569 *||17 Mar 1995||3 Jul 2001||Advanced Cardiovascular Systems, Inc.||Automatic engagement and pressure checking system for an inflation control system|
|US6264659 *||8 Dic 1999||24 Jul 2001||Anthony C. Ross||Method of treating an intervertebral disk|
|US6280456 *||23 Sep 1999||28 Ago 2001||Kyphon Inc||Methods for treating bone|
|US6306177 *||18 Dic 1997||23 Oct 2001||Advanced Bio Surfaces, Inc.||Biomaterial system for in situ tissue repair|
|US6402784 *||10 Jul 1998||11 Jun 2002||Aberdeen Orthopaedic Developments Limited||Intervertebral disc nucleus prosthesis|
|US6416776 *||16 Feb 2000||9 Jul 2002||St. Francis Medical Technologies, Inc.||Biological disk replacement, bone morphogenic protein (BMP) carriers, and anti-adhesion materials|
|US6443988 *||18 Nov 1998||3 Sep 2002||Disc Dynamics, Inc.||Mold apparatus and kit for in situ tissue repair|
|US6468279 *||27 Ene 1998||22 Oct 2002||Kyphon Inc.||Slip-fit handle for hand-held instruments that access interior body regions|
|US6575919 *||24 Oct 2000||10 Jun 2003||Kyphon Inc.||Hand-held instruments that access interior body regions|
|US6602291 *||5 Abr 1999||5 Ago 2003||Raymedica, Inc.||Prosthetic spinal disc nucleus having a shape change characteristic|
|US6607544 *||19 Oct 1999||19 Ago 2003||Kyphon Inc.||Expandable preformed structures for deployment in interior body regions|
|US6623505 *||31 Jul 2001||23 Sep 2003||Kyphon Inc.||Expandable structures for deployment in interior body regions|
|US6645213 *||27 Jun 2001||11 Nov 2003||Kyphon Inc.||Systems and methods for injecting flowable materials into bones|
|US6692563 *||3 Jul 2001||17 Feb 2004||Kyphon, Inc.||Magnesium-ammonium-phosphates cements, the production of the same and the use thereof|
|US6719761 *||2 Feb 2000||13 Abr 2004||Kyphon Inc.||System and methods for injecting flowable materials into bones|
|US6719773 *||19 Jun 2000||13 Abr 2004||Kyphon Inc.||Expandable structures for deployment in interior body regions|
|US6733505 *||15 Nov 2001||11 May 2004||Sdgi Holdings, Inc.||Apparatus and method for loading a prosthetic nucleus into a deployment cannula to replace the nucleus pulposus of an intervertebral disc|
|US6814763 *||1 Mar 2001||9 Nov 2004||Dystar Textilfarben Gmbh & Co. Deutschland Kg||Mediator systems based on mixed metal complexes, used for reducing dyes|
|US6889719 *||3 Jul 2002||10 May 2005||Toyoda Gosei, Co., Ltd.||Plastic pipe and manufacturing method therefor|
|US6908506 *||4 Feb 2004||21 Jun 2005||Kyphon Inc.||Magnesium ammonium phosphate cement composition|
|US6979341 *||18 Abr 2001||27 Dic 2005||Kyphon Inc.||Expandable preformed structures for deployment in interior body regions|
|US20020029083 *||22 Mar 2001||7 Mar 2002||Zucherman James F.||Implantable prosthetic or tissue expanding device|
|US20020077701 *||17 Dic 2001||20 Jun 2002||Kuslich Stephen D.||Annulus-reinforcing band|
|US20020165542 *||11 Abr 2002||7 Nov 2002||Ferree Bret A.||Annulus fibrosis augmentation methods and apparatus|
|US20020173851 *||6 Jun 2002||21 Nov 2002||Mckay William F.||Intervertebral disc treatment devices and methods|
|US20020189622 *||29 Abr 2002||19 Dic 2002||Cauthen Joseph C.||Spinal disc annulus reconstruction method and spinal disc annulus stent|
|US20030040800 *||5 Nov 2001||27 Feb 2003||Li Lehmann K.||Apparatus and method for replacing the nucleus pulposus of an intervertebral disc or for replacing an entire intervertebral disc|
|US20030045937 *||6 Sep 2001||6 Mar 2003||Integrated Vascular Systems, Inc.||Apparatus and methods for treating spinal discs|
|US20030195628 *||13 Feb 2003||16 Oct 2003||Qi-Bin Bao||Method of making an intervertebral disc prosthesis|
|US20030199984 *||11 Jun 2003||23 Oct 2003||Trieu Hai H.||Intervertebral disc nucleus implants and methods|
|US20030220649 *||13 Feb 2003||27 Nov 2003||Qi-Bin Bao||Intervertebral disc prosthesis|
|US20040034427 *||19 Ago 2002||19 Feb 2004||Goel Vijay K.||Bioartificial intervertebral disc|
|US20040091540 *||15 Nov 2001||13 May 2004||Desrosiers Eric Andre||Method for restoring a damaged or degenerated intervertebral disc|
|US20040097927 *||13 Feb 2002||20 May 2004||Yeung Jeffrey E.||Intervertebral disc repair|
|US20050209601 *||9 Nov 2004||22 Sep 2005||Disc Dynamics, Inc.||Multi-stage biomaterial injection system for spinal implants|
|US20060247657 *||27 Abr 2005||2 Nov 2006||Sdgi Holdings, Inc.||Methods and systems for characterizing intervertebral disc space|
|US20070112299 *||26 May 2006||17 May 2007||Stryker Corporation||Hand-held fluid delivery device with sensors to determine fluid pressure and volume of fluid delivered to intervertebral discs during discography|
|US20070173943 *||16 Ene 2004||26 Jul 2007||Dulak Gary R||Artificial nucleus pulposus and method of injecting same|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US7556650||29 Jun 2005||7 Jul 2009||Spine Wave, Inc.||Methods for injecting a curable biomaterial into an intervertebral space|
|US7713303||28 Abr 2005||11 May 2010||Warsaw Orthopedic, Inc.||Collagen-based materials and methods for augmenting intervertebral discs|
|US7720533||20 Dic 2006||18 May 2010||Zimmer Orthobiologicals, Inc.||Apparatus and method for delivering a biocompatible material to a surgical site|
|US7722579||29 Jun 2005||25 May 2010||Spine Wave, Inc.||Devices for injecting a curable biomaterial into a intervertebral space|
|US7731981||23 Ene 2007||8 Jun 2010||Warsaw Orthopedic, Inc.||Collagen-based materials and methods for treating synovial joints|
|US7740660||29 Jun 2005||22 Jun 2010||Spine Wave, Inc.||Methods for treating defects and injuries of an intervertebral disc|
|US7744651||6 Ene 2005||29 Jun 2010||Warsaw Orthopedic, Inc||Compositions and methods for treating intervertebral discs with collagen-based materials|
|US7789912||7 Ene 2005||7 Sep 2010||Spine Wave, Inc.||Apparatus and method for injecting fluent material at a distracted tissue site|
|US7789913||29 Jun 2005||7 Sep 2010||Spine Wave, Inc.||Methods for injecting a curable biomaterial into an intervertebral space|
|US7837733||29 Jun 2005||23 Nov 2010||Spine Wave, Inc.||Percutaneous methods for injecting a curable biomaterial into an intervertebral space|
|US7850730 *||29 Mar 2006||14 Dic 2010||Synthes Usa, Llc||Method and apparatus for implanting a hydrogel prosthesis for a nucleus pulposus|
|US7879103||17 Abr 2006||1 Feb 2011||Musculoskeletal Transplant Foundation||Vertebral disc repair|
|US7918889||27 Feb 2006||5 Abr 2011||Warsaw Orthopedic, Inc.||Expandable spinal prosthetic devices and associated methods|
|US7938836||25 Oct 2005||10 May 2011||Trans1, Inc.||Driver assembly for simultaneous axial delivery of spinal implants|
|US7959683||23 Jul 2007||14 Jun 2011||Musculoskeletal Transplant Foundation||Packed demineralized cancellous tissue forms for disc nucleus augmentation, restoration, or replacement and methods of implantation|
|US8029511||9 Nov 2004||4 Oct 2011||Disc Dynamics, Inc.||Multi-stage biomaterial injection system for spinal implants|
|US8118779||30 Jun 2006||21 Feb 2012||Warsaw Orthopedic, Inc.||Collagen delivery device|
|US8133279||9 Ene 2007||13 Mar 2012||Warsaw Orthopedic, Inc.||Methods for treating an annulus defect of an intervertebral disc|
|US8147517||23 May 2006||3 Abr 2012||Warsaw Orthopedic, Inc.||Systems and methods for adjusting properties of a spinal implant|
|US8157863||16 Jul 2009||17 Abr 2012||Warsaw Orthopedic, Inc.||Devices, apparatus, and methods for bilateral approach to disc augmentation|
|US8197544||27 Feb 2012||12 Jun 2012||Spine Wave, Inc.||Method for distracting opposing vertebral bodies of a spine|
|US8246630||18 Ago 2010||21 Ago 2012||Spine Wave, Inc.||Apparatus and method for injecting fluent material at a distracted tissue site|
|US8317802||16 Ago 2012||27 Nov 2012||Spine Wave, Inc.||System for distracting opposing vertebral bodies of a spine|
|US8337557||29 Jun 2005||25 Dic 2012||Spine Wave, Inc.||Apparatus and kit for injecting a curable biomaterial into an intervertebral space|
|US8357168 *||5 Sep 2007||22 Ene 2013||Spine Wave, Inc.||Modular injection needle and seal assembly|
|US8399619||30 Jun 2006||19 Mar 2013||Warsaw Orthopedic, Inc.||Injectable collagen material|
|US8475532 *||9 Nov 2010||2 Jul 2013||DePuy Synthes Products, LLC||Method and apparatus for implanting a hydrogel prosthesis for a nucleus pulposus|
|US8480757||28 Ago 2006||9 Jul 2013||Zimmer, Inc.||Implants and methods for repair, replacement and treatment of disease|
|US8497121||23 Mar 2012||30 Jul 2013||Zimmer Orthobiologics, Inc.||Method of obtaining viable small tissue particles and use for tissue repair|
|US8518433||15 Dic 2011||27 Ago 2013||Zimmer, Inc.||Method of treating an osteochondral defect|
|US8524268||15 Dic 2011||3 Sep 2013||Zimmer, Inc.||Cadaveric allogenic human juvenile cartilage implant|
|US8632524||21 Jun 2006||21 Ene 2014||Warsaw Orthopedic, Inc.||Injectable biocompatible material delivery system|
|US8652507||22 Dic 2010||18 Feb 2014||Zimmer, Inc.||Juvenile cartilage composition|
|US8765165||23 Ago 2010||1 Jul 2014||Zimmer, Inc.||Particulate cartilage system|
|US8784863||22 Dic 2010||22 Jul 2014||Zimmer, Inc.||Particulate cadaveric allogenic cartilage system|
|US8834914||22 Dic 2010||16 Sep 2014||Zimmer, Inc.||Treatment methods using a particulate cadaveric allogenic juvenile cartilage particles|
|US8876833||30 Abr 2010||4 Nov 2014||Kyphon Sarl||Multi-port delivery system|
|US8979931 *||8 Dic 2006||17 Mar 2015||DePuy Synthes Products, LLC||Nucleus replacement device and method|
|US9138318||15 Dic 2011||22 Sep 2015||Zimmer, Inc.||Apparatus for forming an implant|
|US20050209601 *||9 Nov 2004||22 Sep 2005||Disc Dynamics, Inc.||Multi-stage biomaterial injection system for spinal implants|
|US20060004326 *||29 Jun 2005||5 Ene 2006||Keith Collins||Apparatus and kit for injecting a curable biomaterial into into an intervertebral space|
|US20060004457 *||29 Jun 2005||5 Ene 2006||Keith Collins||Methods for injecting a curable biomaterial into an intervertebral space|
|US20060004458 *||29 Jun 2005||5 Ene 2006||Keith Collins||Methods for injecting a curable biomaterial into an intervertebral space|
|US20060009778 *||29 Jun 2005||12 Ene 2006||Keith Collins||Methods for treating defects and injuries of an intervertebral disc|
|US20060009779 *||29 Jun 2005||12 Ene 2006||Keith Collins||Devices for injecting a curable biomaterial into a intervertebral space|
|US20060009851 *||29 Jun 2005||12 Ene 2006||Keith Collins||Percutaneous methods for injecting a curable biomaterial into an intervertebral space|
|US20060206209 *||8 Ago 2005||14 Sep 2006||Cragg Andrew H||Prosthetic nucleus apparatus and methods|
|US20060265076 *||8 Nov 2005||23 Nov 2006||Disc Dynamics, Inc.||Catheter holder for spinal implant|
|US20080154233 *||20 Dic 2006||26 Jun 2008||Zimmer Orthobiologics, Inc.||Apparatus for delivering a biocompatible material to a surgical site and method of using same|
|US20110276140 *||10 Nov 2011||Edward Vresilovic||Method and apparatus for implanting a hydrogel prosthesis for a nucleus pulposus|
|US20140222009 *||14 Ago 2012||7 Ago 2014||O.P.A. Medical. S.R.L.||Assembly for kyphoplasty procedures|
|WO2007076212A2 *||30 Nov 2006||5 Jul 2007||Disc Dynamics Inc||Nuclectomy method and apparatus|
|WO2011137062A2 *||25 Abr 2011||3 Nov 2011||Kyphon Sarl||Multi-port delivery system|
|Clasificación de EE.UU.||606/90, 623/17.16|
|Clasificación internacional||A61F2/46, A61F2/02, A61B17/88, A61B19/00, A61F2/30, A61F2/00, A61F2/44|
|Clasificación cooperativa||A61F2002/4663, A61B2019/464, A61F2210/0085, A61F2002/30583, A61B17/8836, A61F2002/4694, A61F2002/3008, A61F2002/4627, A61F2002/30062, A61F2002/4688, A61F2210/0004, A61F2002/4677, A61F2002/465, A61F2002/4693, A61B17/8827, A61F2002/467, A61F2/441, A61F2/4601, A61F2/4611, A61B17/8805, A61F2250/0098|
|Clasificación europea||A61B17/88A2V, A61B17/88A4C, A61B17/88A2, A61F2/46B7, A61F2/44B, A61F2/46A|
|9 Nov 2004||AS||Assignment|
Owner name: DISC DYNAMICS, INC., MINNESOTA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:BOWMAN, BRUCE R.;KOHLER, ROBERT;MARTZ, ERIK;AND OTHERS;REEL/FRAME:015982/0321;SIGNING DATES FROM 20041028 TO 20041108