Mechanical loading has been shown to aid in proper differentiation of a number of different types of cells and corresponding tissue to a state closer to the native cells and tissues which must withstand a variety of types of mechanical loading (tensile, compressive, etc.) to function in vivo.
A system is desired in which cells, scaffolds or tissue (engineered or graft) can be loaded and grown while being subject to a variety of mechanical loads. Such a system can aid in the testing and understanding of the mechanical and growth conditions necessary for creating properly conditioned tissue grafts and properly differentiated tissues.
The subject application provides an apparatus for applying mechanical loading to a biological sample, said apparatus comprising: a bioreactor device configured to house the biological sample, and a load application unit for applying mechanical loading to the biological sample housed in the bioreactor device, said load application unit including: a) a first sliding arm for applying mechanical displacement to the biological sample in the bioreactor device in a first predetermined direction; and b) a guide rail coupled to the first sliding arm to limit movement of the first sliding arm such that the first sliding arm moves only in the first predetermined direction when displaced.
Other inventive aspects and features are discussed in the following detailed description.
The device acts as a bioreactor by employing a cell-friendly environment with the use of FDA-compliant material.
Unless defined otherwise, all technical and scientific terms used herein have the meaning commonly understood by a person skilled in the art to which this invention belongs. However, except as otherwise expressly provided herein, each of the following terms, as used in this application, shall have the meaning set forth below.
As used herein, “actuator” means a device for moving or controlling another device or set of devices by converting energy from another source, e.g., a motor, into mechanical motion.
As used herein, “bioreactor device” means, in its broadest sense, any device or system that supports a biologically active environment.
As used herein, “control system” means a device or set of devices which regulates the behavior of other devices. In one embodiment, it can be a computer which automatically or with user interface controls other devices via electronic signals or wireless signals.
As used herein, “design dimension” shall mean the desired dimension to achieve during raw material machining and is determined by the dimensions in the design.
As used herein, “functional” shall mean affecting physiological or psychological functions but not organic structure.
As used herein, “graft” shall mean, in its broadest sense, any device to be implanted during a surgical procedure to transplant tissue without a blood supply, including but not limited to soft tissue graft, synthetic grafts, and the like. The graft can be an allograft, for example, tissue taken from one person for transplantation into another, or an autograft.
An “allograft” is tissue taken from one person for transplantation into another. An “autograft” or “autologous graft” is a graft comprising tissue taken from the same subject to receive the graft. Graft can also be allogeneic or xenogenic. As used herein, “allogeneic” means from the same species. As applied to a graft, allogeneic means that the graft is derived from a material originating from the same species as the subject receiving the graft. “Xenogenic” means from a different species. As applied to grafts, xenogenic shall mean that the graft is derived from a material originating from a species other than that of the subject receiving the graft.
As used herein, “load application unit” means, in its broadest sense, any device or system that applies mechanical loading including, for example, compression, tension, torque, etc.
As used herein, “mechanical loading” shall mean forces applied to a structure or a component which are mechanical in nature, or a mechanical force. Mechanical loading includes, for example, compression, tension, torque, etc.
As used herein, “polymer” shall mean, in its broadest sense, a chemical compound or mixture of compounds formed by polymerization and including repeating structural units. Polymers may be constructed in multiple forms and compositions or combinations of compositions.
As used herein, all numerical ranges provided are intended to expressly include at least the endpoints and all numbers that fall between the endpoints of ranges.
In an aspect of this disclosure, an apparatus for applying mechanical loading to a biological sample is provided, which apparatus comprises a bioreactor device configured to house the biological sample, and a load application unit for applying mechanical loading to the biological sample housed in the bioreactor device, said load application unit including: a) a first sliding arm for applying mechanical displacement to the biological sample in the bioreactor device in a first predetermined direction; and b) a guide rail coupled to the first sliding arm to limit movement of the first sliding arm such that the first sliding arm moves only in the first predetermined direction when displaced.
The above-mentioned apparatus can include various features. For example, in an exemplary embodiment, the bioreactor device comprises: c) a first securing device for securing one end of the biological sample; and d) a second securing device for securing another end of the biological sample opposite to the first end. In another exemplary embodiment, the load application unit further comprises an insert piece to couple the first sliding arm to the first securing device or the second securing device.
In addition, the load application unit can be configured to apply mechanical loading in any one or a combination of directions to the biological sample in the bioreactor device. The mechanical loading can be compression, tension, a hybrid, etc. In one exemplary embodiment, the first predetermined direction in which the sliding arm is displaced is perpendicular to a longitudinal axis of the insert piece. In another exemplary embodiment, the first predetermined direction in which the sliding arm is displaced is perpendicular to a longitudinal axis of the sliding arm.
In another exemplary embodiment, the bioreactor device further comprise clamps, specifically, the bioreactor device can further comprise f) a static clamp for securing one end of the biological sample; and g) a sliding clamp for securing another end of the biological sample opposite to the first end, said sliding clamp being configured for movement in said first predetermined direction. The clamp can be constructed from a polymer or a mixture of polymers which can include, for example, polytetrafluoroethylene (PTFE).
In an exemplary embodiment, the load application unit further comprises a first actuator connected to the first sliding arm for actuating the mechanical displacement of the sliding arm in the first predetermined direction. The load application unit further can further comprise a second actuator and a second sliding arm connected to the second actuator, for applying mechanical displacement to the biological sample in the bioreactor device in a second predetermined direction different from the first predetermined direction. The second predetermined direction can be perpendicular to the first predetermined direction. (See e.g.,
Although
One or more sides of the bioreactor device can have a range of transparency properties that allows the biological sample to be visible to the user through at least one of unaided human vision and microscopy.
The base of the load application unit can be constructed from aluminum. The aluminum is preferably corrosion-resistant and/or aircraft-grade aluminum.
One or both of the sliding arm(s) and the guide rail(s) of the load application unit can be constructed from stainless steel.
The sliding arms of the load application unit and the actuators which actuate the sliding arms can provide for a range of motions. In one exemplary embodiment, the first and/or second sliding arm of the load application unit displaces the bioreactor device linearly. In another embodiment, the first sliding arm displaces the biological sample in the bioreactor device linearly in the first predetermined direction.
In one embodiment, the first and/or second actuator of the load application unit actuates linear displacement of the one or more of the sliding arms. In another embodiment, the first actuator actuates linear displacement of the first sliding arm in the first predetermined direction and the second actuator actuates linear displacement of the second sliding arm. The actuator(s) can be powered by a high-precision stepper motor.
In another aspect, the apparatus further comprises a control device configured to control the at least one of the first and the second actuator and/or at least one of the first and the second sliding arm. For example, such control can be effected through computer and one or more sensors.
In addition to the features described above, the apparatus disclosed herein can further comprise bearings configured to guide, in conjunction with the guiding rail, the displacement of the first sliding arm. For example, a ball bearing system connecting the sliding arm and the guiding rail can be used.
The apparatus provided by the present invention can further comprise one or more securing parts for securing the bioreactor devices onto the load application unit. The parts can include stop blocks and/or clamps. The stop blocks and/or clamps can be constructed from a polymer or a mixture of polymers which can include, for example, polyoxymethylene.
All combinations of the various elements described herein are within the scope of the invention.
The specific embodiments and examples described herein are illustrative, and many variations can be introduced on these embodiments and examples without departing from the spirit of the disclosure or from the scope of the appended claims. Elements and/or features of different illustrative embodiments and/or examples may be combined with each other and/or substituted for each other within the scope of this disclosure and appended claims.
The present disclosure is directed to a custom-made multi-part apparatus (the “bioreactor assembly”) that can be used to apply mechanical stimulation to biological samples, such as experimental scaffolds or biological grafts intended for tissue repair or regeneration. The bioreactor assembly can be used to grow tissue engineered grafts as well as condition allografts or autografts. The bioreactor assembly can also be used to research into fundamental questions such as the effects of bioreactor culture or biomechanical stimulation on stem cell differentiation as well as cell-matrix interactions.
The bioreactor assembly can be made of two separate components. A first component can be a bioreactor device that includes a casing that can house the biological sample, such as a scaffold. The second component can be a load application unit for applying mechanical stimulation to the biological samples housed in the bioreactor device.
The bioreactor device provides the necessary environment for mechanical stimulation and/or mechanical conditioning of a cell/graft culture. The bioreactor device may be constructed from biocompatible, FDA-approved materials. Thus, the bioreactor device can be used with both tissue engineered scaffolds and biological grafts. Such a bioreactor device is illustrated in
The bioreactor device may be configured to meet three primary goals: 1) ease of use, 2) high sample-to-size ratio and 3) combine graft loading and culture. The bioreactor device parts, fabrication and assembly can be chosen and designed such that it can be fabricated reproducibly and economically. For example, the bioreactor device parts can be designed with nominal and commercially available dimensions. All or portions of the bioreactor device, such as the bioreactor device base, luer valves, and/or device tubing, may be designed to take advantage of commercial off-the-shelf components. Such a design criterion can result in relative ease in fabrication and assembly of the bioreactor device.
As shown in
The bioreactor device can also include a custom-made scaffold cutting board and/or bioreactor device clamp design. With such a configuration, the effort required in mounting a scaffold or graft can be minimized. Clamps as shown in
Connection of the bioreactor device to the load application unit can be effected using a place-and-pin design. The bioreactor device can also be constructed with a relatively low profile characteristic with respect to the number of experimental samples it can hold. For example, the bioreactor device may be designed to have a 150% increase in space efficiency compared to other tensile loading designs. The bioreactor device may also be designed to have the ability to load biological samples, such as scaffolds, without unwanted deformation during the mounting process. The high sample-to-size ratio allows the bioreactor assembly to hold 40 samples per incubator shelf, and at least 20 samples per experimental strain variable. The bioreactor device also gives the user more degrees of observation and experimentation as compared to prior methodologies.
As shown in
Mechanical loading of the bioreactor device is applied by the sliding arm of the load application unit. The sliding arm is connected to the actuator, which may be any type of precision actuator known in the art. For example, the actuator may be a linear actuator powered by a high-precision stepper motor. The sliding arm rides along a precision sliding system. The sliding system may be made from a metal, for example, stainless steel. Guide blocks slide over the rails by means of bearings, for example, ball bearings, to provide smooth and consistent movement.
The bioreactor device may be secured in place in the load application unit by stop blocks and fixture clamps. The stop block and fixture clamps may be constructed from a polymer material, for example, polyoxymethylene (POM, Delrin®). Such a polymer material selection provides a rigid stopping structure similar to metal material selection but without the risk of scratching the bioreactor device base. Furthermore, the fixture clamp is able to accommodate any discrepancies in bioreactor device dimensions by means of an adjustable head. Cover housing can be incorporated in order to protect each actuator section, as shown in
As shown in
Such a controller may tackle the form of, for example, a computer, network-enabled computer, or independent controller device. The controller can also be configured with the capability to drive multiple motors and respective actuators simultaneously. For example, the controller may drive up to four (4) separate stepper motors. Displacement profile(s) can be customized to an experimental protocol by varying the frequency of displacements, desired peak displacement, time of application and other similar profile parameters.
Furthermore, the bioreactor assembly as described herein may be configured to apply loads simultaneously in different profiles: tensile, compressive or a hybrid of both. Desired duty cycles can be set via the central controller. Because the load application unit can have two actuators, it has the versatility to run in a hybrid mode where part of the load application unit executes a tensile loading profile and another part of the load application unit executes a compressive loading profile. The bioreactor device can also be modified to be used as a compression bioreactor by removing the distance rods and turning the device 180° from its initial position. A force transducer can be placed in-line with the sliding portion of the bioreactor device in order to measure real-time force reactions.
The characteristics of the bioreactor assembly described herein enable flexibility in mounting either tissue-engineered scaffolds or biologically-derived soft-tissue grafts or scaffolds. The bioreactor device enable high-throughput as it is able to hold about five times more samples than most prior mechanical stimulation systems and has the capacity to hold up to forty samples using significantly less space. With minimal modifications, the bioreactor device can be rotated 180° to accommodate either compression or tensile loading profiles. The bioreactor assembly also allows for experiments to run simultaneously with different loading profiles and multiple chemical stimuli per individual loading profile. For example, in the bioreactor assembly illustrated in
Furthermore, the foregoing description applies, in some cases, to examples generated in a laboratory, but these examples can be extended to production techniques. For example, where quantities and techniques apply to the laboratory examples, they should not be understood as limiting. Where noted above, disclosed dimensions and materials are for illustration purposes only and are not meant to be limiting.
It is, therefore, apparent that there is provided, in accordance with the present disclosure, a bioreactor assembly for mechanical stimulation of biological samples. Many alternatives, modification, and variations are enabled by the present disclosure. Features of the disclosed embodiments can be combined, rearranged, omitted, etc., within the scope of the invention to produce additional embodiments. Furthermore, certain features of the disclosed embodiments may sometimes be used to advantage without a corresponding use of other features. Accordingly, applicants intend to embrace all such alternatives, modifications, equivalents, and variations that are within the spirit and scope of the present disclosure.
Further aspects, features and non-limiting details are described in the following sections which are set forth to aid in an understanding of the subject matter.
The bioreactor assembly described herein (also the “Assembly”) has essentially two components, the bioreactor device (also the “Device”) and the load application unit (also the “Scaffold Loading System” or the “SLS”).
The bioreactor assembly was designed to address several research limitations present for the study of cell response. Primarily, these limitations arise from the absence of equipment to run large-scale stimulation tests, with the capability to incorporate and control mechanical and chemical stimulation parameters, as well as other experimental variables.
The bioreactor system described herein is a custom-made, multi-unit bioreactor system that can be used to apply mechanical stimulation to experimental scaffolds or biological grafts in order to study the behavioral response of cells seeded on the scaffold. Moreover, it can also be used to grow tissue engineered grafts and condition allografts or autografts.
Referring to
Another advantageous characteristic of the Device is its low profile characteristics relative to the number of experimental samples it can hold. The current design results in a 150% increase in space efficiency compared to the previous tensile loading design, and the ability to load the scaffolds without the danger of deforming them during mounting. This high sample-to-size ratio allows the Assembly to hold 40 samples per incubator shelf, and at least 20 samples per experimental strain variable.
The Device also gives the user more degrees of observation and experimentation that most designs currently available, while being made from biocompatible materials compliant with FDA standards. The clear acrylic base and polycarbonate cover give the user about 360 degrees of visibility on the scaffold and cellular response. In addition, the Device's translucent casing design allows for in vitro scaffold image acquisition using conventional and fluorescence microscopy. Scaffold integrity and load transfer is achieved by Teflon® clamps. These Teflon® clamps allow for smooth sliding on the Device base while keeping the cells from proliferating on areas other than the scaffold, since cells do not attach on Teflon®. Media and any possible liquid spill mishaps are contained within the Device by a silicone rubber gasket.
A preferred embodiment is shown in
However, due to the gasket being absent, leakage from the sides of the device is possible. On the other hand, this problem is minimal since pressure from handling and pressing on the cover is enough to prevent most leakage. However, depending on the elbow mounting, leaking may still occur. Therefore, it is preferable to seal the elbow with silicone on the inside before threading the elbow.
A main purpose of the base of the bioreactor device is to create an environment that is suitable for cell growth, and provide a platform to enable dynamic loading. It is also desirable that the base be durable and able to endure sterilization.
Therefore, in a preferred embodiment, the base of the Device is machined from a solid block rather than manufactured by using any acrylic solvent to weld together five pieces cut with a laser cutter. Because this base is milled from a solid block, the chance of leaking occurring through the seams in the bioreactor device is reduced or eliminated.
In a preferred embodiment, Teflon® pieces manufactured have a much tighter tolerance as compared to previous designs and do not leave any space between the walls of the device and the components. Also, the height of the Teflon® pieces was reduced from previous designs so that even if gaps occur or if capillary action is occurring, there is no path all the way to the top of the device. Removing this continuous pathway should reduce or prevent chances of leaking by capillary action.
The Device cover in an exemplary embodiment of the present invention is shown in
In a preferred embodiment, a design similar to a standard petri dish was employed for the Device cover. (See
Large mechanical forces exerted on the scaffolds require that the SLS have a strong base to withstand deformation, while remaining lightweight so that most users can carry it. With this in mind, the SLS base, as well as any other custom-manufactured metal part from the SLS, is made from ultra-corrosion resistant, aircraft-grade aluminum. This material provides a lightweight, tough base that can withstand the humid environment of a biological incubator, while also being easy to manufacture. The Device applies mechanical load by a sliding arm that is connected to the actuator. This arm rides along a precision sliding system made from stainless steel. The guide blocks slide over the rails by means of ball bearings for a smooth and consistent movement. Device placement is secured by a Delrin® stop block and fixture clamps. Delrin® provides a rigid stopping structure like metal would without the risk of scratching the acrylic base, while the fixture clamp is able to accommodate any discrepancies in Device dimensions by means of an adjustable head. For further protection against fungi spores and other airborne pathogens, a SLS cover housing covers each actuator section (see
Two linear actuators, powered by two stepper motors, provide the force displacement. In order to keep the effects of temperature variations or magnetic fields on the incubator environment to a minimum, the SLS motor and the Assembly are placed in two different locations. Motor and actuator pairing is accomplished by a heavy duty sealed flexible coupling, which permits locating the motors outside the incubator. The stepper motors apply the mechanical displacement profile by means of a central controller, which has the capability to drive up to four (4) separate stepper motors. Displacement profile(s) can be customized to the experimental protocol by varying the frequency of displacement, desired peak displacement, time of application and other similar profile parameters.
Additional features are integrated in the design for different applications that may arise in the future. The Assembly has the capability to apply loads in three different profiles: tensile, compressive or hybrid. Because the Assembly is includes two stepper motors, it has the versatility to run in hybrid mode where part of the Assembly executes a tensile loading profile and another part of the Assembly a compressive profile. The Device can be modified to be used as a compression bioreactor by removing the distance rods and placing the device in a 180° orientation from tensile loading. In addition, a force transducer can be placed in-line with the sliding portion of the Device in order to measure real-time force reactions.
Two embodiments of a SLS plate are shown in
In
In
Raw materials are those materials which are bought in a predetermined size and brought to design dimensions with fabrication techniques. As a general rule, it is best to acquire the raw material with dimension(s) as close to those of the desired design dimension(s). Most of the raw materials described herein can be purchased through McMaster Carr (Elmhurst, Ill.).
When working with a raw material it is preferable to do the following:
Other factors are preferably taken into account if the piece is to be used in a specific way. An example of the implementation of these factors is the system plate. Aluminum was chosen because of its lightweight properties and ease of fabrication. Further study showed that its Al 7075 alloy was the top choice because of its superior machinability, strength and corrosion resistance as well as its lightweight characteristic. This type of alloy is the same used in aircrafts because of these desirable characteristics.
The SLS system is subjected to humid/wet environments since its main experimental location is inside a cell culture incubation system. In addition, its main component (the Device) is generally be filled with liquid, which might accidentally spill. Because of the ionic nature of the cell culture media, the system plate reacts with the media as pitting corrosion when both come in contact for a prolonged period (this does not happen with DI water, as previously tested).
Although Al 7075 is the main metallic component of the SLS, it is preferred to clean every piece of the SLS system prior to assembly. Failure to do so might allow foreign metals to remain stuck between parts and initiate a corrosive chemical reaction. For a greater measure of corrosion resistance, passivation the surface of the pieces is recommended (anodizing is also possible, but might be more expensive).
Before the actual passivation of the material, it is preferably that the piece be thoroughly cleaned. Only after doing so can the piece be subjected to the chemical reactions necessary for passivation. It is important to note that the proposed process takes approximately 9 days (Shih, 1992).
The passivation duration is determined by the amount of desired passivation. Because cell feeding is usually done every 2-4 days depending on the cell, and assuming that any liquid spilled during that time is cleaned, passivation time should take into account that the corrosive liquid only touches the metal surface for the 2-4 day time frame. With this in mind, it is suggested the sample be submerged in a 10 mM CeCl3 solution for 7 days at room temperature. For the case of extreme increased exposure period (+20 days), passivation time can be done for 30 days with a solution of 10 mM CeCl3.
Though chromate conversion coating is a more popular passivation method, it has been shown to produce hazardous by-products. This method has shown to provide equal or better corrosion resistance.
Make sure each piece can be fabricated from beginning to end without interruption. This ensures that the same reference point, tool surface characteristics, tool surface temperature and machining technique is used throughout the piece machining life, and decreases any inconsistencies in the piece dimensions. It should also be noted that in order to acquire a shine finish, the piece should be polished after machining.
The SLS is fabricated from raw materials machined using a mill and a laser-cutter. Sawing and polishing are supplementary equipment that allow for easier machining to the design dimension.
The horizontal band saw is used to cut raw materials to a more manageable dimension close to the design dimension. It is preferred that this cut be made with enough material left on the raw material to do a successful facing and final cut. This band saw type can be used for all materials, but is usually reserved for tougher materials such as steel and other hard metals, or any large (long) piece that needs to be cut down.
More versatile, the vertical band saw is used for closer cuts. Only plastics should be cut with this saw, and with the appropriate band saw blade, some soft metals like aluminum (depending on the type of aluminum, for example, Al 7075 should not be cut using the brand saw because of its toughness). It is best to accommodate the roller bearing on the blade track as close to the cutting face as possible.
Before starting to mill the piece towards the design dimension, make sure to face the piece in order to assure the square geometry of the sides. It is important to note several factors that are preferably taken into consideration when milling:
Made by Universal Laser Systems, the Versa Laser uses a 30 watt, far-infrared CO2 laser beam capable of cutting through most plastics at 1 inch thick and engraves most metals. The laser-cutter proves to be extremely reliable in fabricating the Device and the SLS cover, as both are made from acrylic; a material superbly easy to work with using this equipment. All that has to be done in order to cut a piece is draw the desired geometry on Corel Draw and print it on the laser-cutter.
This section should be used as a guideline in the fabrication of the SLS. Several different set-ups were attempted before arriving to the most effective (which is presented here), but are by no means the only methods capable of arriving to the desired result.
It is preferred that the cutting tool (drill bit or end-mill) be thoroughly oiled at all times. This results in a cleaner finish, increased tool life, decreased temperature rise and vibrations. This process is time consuming and should be taken into consideration before starting the machining of the part.
It is also preferred to adequately clamp any oversized piece. Failure to adequately clamp an oversized piece can ultimately shatter the cutting tool and/or damage the piece's surface.
Made from aircraft-grade, corrosion-resistant Al 7075, the plate exhibits excellent mechanical characteristics and machinability with an impressive light-weight feature. To machine the stock ordered from McMaster, the plate is first placed on the mill table by removing the vice, and clamping it down with the screw-down bumpers. After doing so, follow these guidelines:
It is preferable to keep the tool clean from shavings and always oil the piece surface during machining. Another aspect to have in mind is tool wear, as it can alter final piece dimensions. In order to minimize its impact on final dimensions, measure the actual tool dimensions with a caliper and use that for machining calculations.
Fabrication of the arm is facilitated by a program that was written to machine the piece in a three-step process: milling starts on the left, followed by the right side and finishing by milling the center portion As with any new program, test it by running it without cutting the piece. Before running the program, make sure that the middle portion of the arm is clamped on the vice with supporting clamps on either side. Also, it is preferred that the supporting clamps do not bend the arm. The supports can come from a variety of pieces that are found in the machine shop, but all should be as close to being square or right angles as possible to minimize bending. Finally, make sure that the clamps are out of reach of the cutting tool. For the holes, make sure to always have the top surface orientation in mind, especially for the holes used to hide the screw heads.
The Rail Spacer takes on two aspects of the Arm and Plate fabrication. Its oversized profile makes is preferable to be clamped like the Arm, and its hole pattern follows that of the Plate (i.e.: the same program for the Plate can be used here as well). As always, it is preferred to have in mind the orientation of the front part of the Rail Spacer and its association to the Plate.
All measurements and hole number can be found on the drawing of the respective piece.
Device fabrication is easier since bulk fabrication is possible once a single piece is fabricated correctly, so care should be taken to fabricate the first piece as close to the design dimension as possible. For pieces that have extruding features (i.e.: top static clamp and top carriage clamp), a tolerance of −0.001″ should be strictly followed, as anything less results in scaffold slippage.
When working with Teflon®, clamping for should be just enough so that the piece does not move when pushed. This small clamping force ensures that the piece does not bow after the cutting tool begins removing material. Because Teflon® is very compliant, the cutting tool simply passes through the piece with minimal resistance.
Fabrication of the Device base and cover is done with the in-house laser-cutter, making fabrication of the Device extremely easy and repeatable.
Third party parts are those parts that come ready to assemble into the SLS with little or no modification. A detailed list of parts is shown in Table 1.
Assembly is preferably done after all of the required materials are available. This allows the person assembling the system to calibrate and tweak the system all at the same time. Also, if the system is to be buffed or passivated, any of these two processes should be done before assembly takes place. Finally, in order to minimized corrosion and contamination, make sure that the system is completely washed from machining particulates and grease, and that no debris is left between two adjoining surfaces.
Finish the machined pieces by thoroughly cleaning and degreasing them, followed by any surface treatment(s). As part of the design goal, the SLS is easily put together following these guidelines:
Before using the SLS System, make sure to make any final adjustments and corrections. It is important to note any jerky motion or “sticking” of the SLS arm as well as any part that rotates or shifts out of place as this could interfere with force transfer to the experimental specimen.
Depending on the origin of the Device (whether acquired from a third-party entity or fabricated in-house) minimal assembly is needed. For either case, all Teflon® parts are fabricated in the machine shop and the Device cover with the laser-cutter.
Freely apply the silicone adhesive on the bottom static clamp, and slowly apply pressure on the clamp. This ensures that no air bubbles are left between the clamp and the device base
By acquiring the Device from a third party entity, previous results have given a tolerance of ±0.034″ which, with the current Device clamping mechanism, is not acceptable since it complicates the System by adding another feature that needs calibration. A tolerance of ±0.01″ or less is deemed acceptable for the current application.
The only assembly step for this method is adhesion of the bottom static clamp. Apply the silicone RTV adhesive on both surfaces of the piece that come in contact with the Device base.
After laser-cutting the Device pieces, proceed to assemble the Device by adhering the pieces with acrylic weld (Weld-on #3; McMaster Carr). For correct assembly, the sides are preferably parallel to each other and perpendicular to the bottom. This can be achieved by creating a mold to drop each side in and then applying the acrylic weld, or by using right-angled and parallel straightedges to correctly orient the pieces individually. Either of these processes can be used to assemble the base and the cover. Finally, proceed to place the bottom static clamp as described above.
In both methods, addition of the 90° feeding port elbow is done after placing the bottom static clamp. It is preferable to do so afterwards in order to err on the side of caution, in case the bottom static clamp is fabricated thicker than intended, over-lapping the drilled hole. Although the elbow has a #10-32 thread, it is best to tap the hole with a drill bit one size smaller than suggested in order to attain a tighter fit. Also, over-tighten the elbow can cause the hole to crack when placed in the incubator due to stress relaxation. Covering the threads with the RTV silicone prior to screwing the elbow onto the Device might help prevent any leaking problems.
Several iterations of the Device were proposed before arriving at the version described supra. A number of alternative designs proposed are illustrated in
5.1 Device 2i.1 (
Device 2i.1 comprises polytetrafluoroethylene (PTFE) clamps, backing and slider.
The transparent material considered for the bioreactor device casing include: a) glass, which is relatively frictionless, clear, autoclavable and brittle, but hard to machine; b) polycarbonate which is biocompatible, clear, strong, easy to machine. However, polycarbonate looses optical properties when machined and is not autoclaveable; c) acrylic which is clear and easy to machine but not autoclavable or biocompatible.
Further modifications considered include:
Device 2i.2 is designed with the same materials as the previous version.
Device 2i.2 is more compliant to established mesh cutting dimensions (5×6 cm) for 5 meshes (1×6 cm each), with some deviations (5×6.7 cm) due to manufacturing process limitations.
Also, gauge length of 4.14 cm (manufactured) vs. 4 cm (current) is even more precise since it is more stringent for mesh characterization.
Compared to Device 2i.1, Device 2i.2 has increased dimensions for easier manufacturing and screwing applications. Also, a total of 0.5″ (¼+⅛+⅛) on each clamp is used for clamping to allow for the established mesh length of 6 cm (real→6.667 cm). In addition, a 1⅜″ distance (4.14 cm) is left as the gauge length, for a width-to-length ratio of approximately 1:4. Finally, the space left accounts for a strain of 25%.
Further modifications considered include:
Compared to previous versions of the Device, Device 2i.3 includes the following modifications: a) incorporating rubber gaskets to prevent cover leakage; b) fabrication of clamps for cover clamps and lead screw placement; c) using Delrin® as cover clamping material; d) elimination of leakage from the side walls; e) introduction of static phase.
Further modifications considered include:
Compared to previous versions of the Device, Device 2i.4 includes the following modifications: a) addition of flat-head screws to the clamps to ensure a secure grip and seal; b) removal of Delrin® grips and overhead lead screw assembly; c) use of a syringe-style attachment on the carriage for inline strain application; and d) ensuring enclosure of the internal chamber of the bioreactor device.
Further modifications considered include:
For Device 2i.5, use of an overhead approach is reconsidered, since strain application can occur by straining system. Compared to previous versions of the Device, Device 2i.5 includes the following modifications: a) removal of syringe-type lead shaft and reintroduction of connecting rod on carriage; b) pushing cover slit closer to edge to ensure effective usage of space and allowing for slit covering by strain system arm; c) custom fabricating base made from acrylic treated for improved resistance to UV degradation and scratching; and d) change gasket thickness from ⅛ inches to 1/16 inches or 1/32 inches.
Further modifications considered include:
This application claims the benefit of U.S. Provisional Application No. 61/120,580, filed Dec. 8, 2008, the entire contents of which are hereby incorporated by reference herein. Throughout this application, certain publications are referenced. Full citations for these publications, as well as additional related references, may be found immediately preceding the claims. The disclosures of these publications are hereby incorporated by reference into this application in order to more fully describe the state of the art as of the date of the invention described and claimed herein.
Filing Document | Filing Date | Country | Kind | 371c Date |
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PCT/US09/06453 | 12/8/2009 | WO | 00 | 1/10/2012 |
Number | Date | Country | |
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61120580 | Dec 2008 | US |