Additive Manufacturing of Channels

Abstract

A method is disclosed for 3D printing of soft polymeric material such as a hydrogel or elastomer for scaffolds or devices with embedded channels with tunable shape and size such as a channel inner diameter). The method utilizes extrusion based printing of polymer solutions usually referred as direct ink writing (DIW) or BioPlotting, and requires sequential printing of a photocurable polymer solution, herein, referred as the matrix material, and a sacrificial polymer solution that may dissolve in an aqueous media.

Claims

1-6. (canceled)

7. A method for making a 3D scaffold, comprises: directly and sequentially printing a photocurable matrix material and a photocurable sacrificial material in a single step by a dual extrusion based printing; fabricating a vascularized scaffold; and wherein the photocurable matrix material and sacrificial material is not a shear thinning material, and the sequential printing of the sacrificial material is within the matrix material; forming an embedded channels having a diameter either same or varied within a range of about 100 μm-500 μm; and performing the following steps: (i) dual printing the uncured matrix material up to a specific thickness for forming a printed layer for the printing of the photocurable polymer matrix material layer; (ii) exposing the matrix material to a light source after each of the printed layer, and partially crosslinking the uncured matrix material layer to form a partial crosslinking layer to allow self-supporting of the matrix material; (iii) printing a second uncured matrix material layer on top of the partial crosslinking layer; (iv) printing the sacrificial layer with a sacrificial material within the second uncured matrix material layer; (v) exposing the partial crosslinking layer and the second uncured matrix material layer to the light source after printing of the sacrificial material inside the second uncured matrix material layer; (vi) printing a new layer of uncured matrix material on top of the second uncured matrix material layer that is now cured; repeating above (i) through (vi) steps to create a vascular scaffold in a desired thickness; exposing the scaffold to the light source to fully crosslink the scaffold after printing and the desired thickness is achieved; and immersing the scaffold into an aqueous solution to remove the sacrificial material for the formation of the plurality of embedded channels.

8. The method of claim 7, wherein the vascularized scaffold is a device.

9. The method of claim 7, wherein the fabricating further comprises: forming the embedded channel using the dual extrusion based printing; and implementing the printing of the sacrificial material within the photocurable matrix material after the matrix material layer is partially cured by exposure to a light source.

10. The method of claim 9, wherein the implementing step further comprises placing an extrusion needle only within an uncured matrix layer for free motion movement of an extrusion needle without using shear thinning behavior material for the matrix material.

11-20. (canceled)

21. A method for making a 3D scaffold, comprises: printing a photocurable polymer matrix material layer and a sacrificial polymer material layer; and wherein the sacrificial polymer material layer is printed directly within the freshly printed photocurable matrix material layer.

22. The method of claim 21 further comprises: placing an extrusion needle only within an interface layer that is partially crosslinked for free motion movement of the needle without using a shear thinning material; and wherein the printing is done sequentially.

23. The method of claim 7, wherein the matrix material is a photo-curable material without shear thinning behavior.

24. The method of claim 7, wherein the printing further comprises creating a vascularized scaffold in a single step using dual extrusion printing.

25. The method of claim 10, wherein the vascularized scaffold is a hydrogel with embedded channels for vascularization.

26. The method of claim 10, wherein the vascularized scaffold is a soft microfluidic device made from an elastomer or a hydrogel.

27. A method for making a 3D scaffold, comprises: directly and sequentially printing a photocurable matrix material and a photocurable sacrificial material in a single step by a dual extrusion based printing; fabricating a vascularized scaffold; and wherein the photocurable matrix material and the sacrificial material is not a shear thinning material, and the sequential printing of the sacrificial material is within an interface of the matrix material.

28. The method of claim 27, wherein the vascularized scaffold is a device.

29. The method of claim 27, wherein the fabricating further comprises: forming an embedded channel using the dual extrusion based printing; and implementing the sequential printing of the sacrificial material within an interface layer of the photocurable matrix material after the matrix material is partially cured by exposure to a light source.

30. The method of claim 29, wherein the implementing step further comprises placing an extrusion needle only within the interface layer for free motion movement of an extrusion needle without using shear thinning behavior material for the matrix material.

31. The method of claim 27, further comprises: (i) dual printing a matrix material up to a specific thickness for forming a printed layer for the printing of the photocurable polymer matrix material layer; (ii) exposing the matrix material to a light source after each of the printed layer, and partially crosslinking the printed layer to allow self-supporting of the matrix material; (iii) printing the sacrificial layer with a sacrificial material for the printing of the sacrificial polymer material layer; (iv) exposing the sacrificial layer to the light source after printing of the sacrificial material; (v) printing a new layer of matrix material; repeating above (i) through (v) steps to create a vascular scaffold in a desired thickness; exposing the scaffold to the light source to fully crosslink the scaffold after printing and the desired thickness or the human scale is achieved; and immersing the scaffold into an aqueous solution to remove the sacrificial material for a formation of channels.

32. The method of claim 27, wherein a thickness of the matrix material is manually determined by an end user.

33. The method of claim 27, wherein the sacrificial material is 100-1000 microns thick depending on a desired channel size.

34. The method of claim 31, wherein the aqueous solution is a phosphate buffer solution, (PBS).

35. The method of claim 27, further comprises surface modifying a glass slide, and wherein the printing is done on the surface modified glass slide or microscope cover slip for easy handling of the scaffold.

36. The method of claim 35, where the surface modifying is done using 3-(trimethoxysilyl) propyl methacrylate to allow covalent cross linking of the matrix material to the glass slide.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0021] To assist those of skill in the art in making and using the disclosed method to make a device using 3D printing and associated systems and methods, reference is made to the accompanying figures, wherein:

[0022] FIG. 1 shows views outlining a printing method to create a channel embedded in a 3D hydrogel, in accordance with one embodiment of the present disclosure;

[0023] FIG. 2 shows views outlining one embodiment of a post-printing method to fully crosslink the matrix hydrogel and dissolve the sacrificial hydrogel to create channels;

[0024] FIGS. 3A-3D show 3D design, and specifically (Top Row) CAD designs of the hydrogel scaffolds with channels (light gray: matrix; dark gray: sacrificial). (FIGS. 3A-D) Pictures showing the printed scaffolds after removal of the sacrificial regions: (FIG. 3A) channels with varying channel diameter, (FIG. 3B) two-layer channel structure (channels are in different planes), (FIG. 3C) interconnected elliptical channels, and (FIG. 3D) channels forming NJIT. Coarse channels (500 μm in diameter) are printed for visual clarity and easy access with a regular size needle, but 100 μm channels can be printed;

[0025] FIGS. 4A-4C show 3D printed structures, and feasibility studies showing (Left FIG. 4A) a schematic of a channel design, and (Center FIG. 4B) a top view of an actual sample having the channel design of FIG. 4A; 3D printed construct with Pluronic doped with red food coloring; and (Right FIG. 4C) confocal images of the channels in FIG. 4B taken at within the region of the black rectangle in Right and perfused with methacrylated rhodamine containing PBS, wherein the channels are smooth and cylindrical in shape with width equal to ˜P500 μm and scale bars are 500 μm and;

[0026] FIG. 5 shows a flow chart to create a channel embedded in a 3D structure, in accordance with one embodiment of the present disclosure.

DETAILED DESCRIPTION

[0027] Vascularization is a major limitation for development of human-scale functional tissues or organs. Fundamentally it requires ability to create channels within 3D soft scaffolds that mimics human tissue. Creating well defined channels within 3D hydrogels and/or elastomers are also important for development of soft devices towards organ-on-a-chip systems, such as but not limited to 3D tissue/disease models, to detect disease or screen for drugs. The present disclosure addresses this major gap in creating channels within soft 3D polymeric systems using additive manufacturing. Although additive manufacturing is utilized to create channels previously, this present novel approach eliminates the use of specially designed printers, specialty shear thinning material, the requirement for multiple steps, and the use of excess materials. This new approach is suitable for any photocurable hydrogel and elastomer formulation with the use of a sacrificial polymer ink such as polymers or hydrogels that are soluble in an aqueous media.

[0028] Exemplary embodiments are directed to 3D printing of soft polymeric scaffolds or devices. It should be understood that embodiments can generally be applied to other scaffolds or devices.

[0029] In one embodiment, a method is disclosed for 3D printing of soft polymeric (hydrogel or elastomer) scaffolds or devices with embedded channels with tunable shape and size (i.e., channel inner diameter). The method utilizes extrusion based printing of polymer solutions usually referred as direct ink writing (DIW) or BioPlotting, and requires sequential printing of a photocurable polymer solution referred herein as the matrix material, and a sacrificial polymer solution, i.e., preferable to dissolve in an aqueous media such as phosphate buffer saline (PBS).

[0030] In this embodiment, the fabrication process starts with 3D printing several layers of matrix material. Matrix material could be any photocurable hydrogel ink. The ink is not required to self-support itself after printing, which allows the use of a wide range of materials. After printing of each layer, the printed matrix solution is exposed to light for a very short time (˜10 s) to partially cure the printed layer. This allows the matrix hydrogel to self-support itself. When the desired matrix material height (thickness) is reached, one additional layer of matrix material is printed but not exposed to light. The sacrificial material is directly printed within this matrix layer. This uncrosslinked matrix layer supports the printed sacrificial polymer/hydrogel. The system is then exposed to light to partially crosslink the matrix layer. Then another layer of matrix material is printed followed by light exposure. This process is repeated as needed to reach the final desired scaffold/device thickness.

[0031] The 3D printed construct is exposed to light to fully crosslink the matrix polymer, such as a hydrogel or elastomer, and immersed in an aqueous media to dissolve the sacrificial polymer or hydrogel. Dissolution of the sacrificial polymer/hydrogel leads to channel formation within the matrix hydrogel or elastomer. This method allows creation of channels within multiple print layers (different regions within z-axis) by printing the sacrificial polymer/hydrogel at the desired print layers (heights).

[0032] FIG. 1 shows views outlining one embodiment of a printing method. The method involves 3D printing several layers of matrix material. A dual print-head with light source 100 is utilized in the method. The reference numeral 100 comprises a matrix ink print-head, a sacrificial ink print-head and a light source as shown in FIG. 1. The portion of reference numeral 100 (matrix ink print-head, sacrificial ink print-head, and/or light source) that is closest to the shown layer indicates what portion is being utilized at that time during the method. A first matrix layer 101 is printed using a matrix ink and partially cured for a certain period of time to form a partially cured matrix layer 102. In one embodiment, the first matrix layer is partially cured using a light source for around 10 seconds. The partial curing time could vary depending on several factors, such as the material. A second matrix layer 103 is printed on the first matrix layer, which has been partially cured. A sacrificial material 104, such as a polymer or hydrogel, is printed using sacrificial ink within the second matrix layer. In one embodiment, the sacrificial material is printed within the second matrix layer before the second matrix layer is exposed to light. The second matrix layer is sized to support the sacrificial material. The first matrix layer, the second matrix layer, and/or the sacrificial material are partially cured as shown in 105 for a certain period of time to crosslink the second matrix layer. In one embodiment, only the second matrix layer is exposed to light in this step. A third matrix layer 106 is printed on the second matrix layer. The first matrix layer, the second matrix layer, the sacrificial material, and/or the third matrix layer are partially cured as shown in 107 for a certain period of time to crosslink the third matrix layer. In one embodiment, only the third matrix layer is exposed to light in this step.

[0033] A 3D printed construct is formed, which includes the first matrix layer, the second matrix layer, the sacrificial material, and the third matrix layer in this embodiment. While only three matrix layers and one sacrificial layer are shown in FIG. 1, the number of matrix layers and sacrificial layers could vary depending on the embodiment.

[0034] FIG. 2 are views outlining one embodiment of a post-printing method. The method involves curing of the 3D printed construct to crosslink the matrix polymer for a certain period of time. In one embodiment, the 3D printed construct is fully cured as shown in step 201 using a light source, and depending on the implementation, the time of cure is for around 4 minutes. The curing time could vary depending on several factors, such as the material. The 3D printed construct is then immersed as shown in step 202 in an aqueous media to dissolve the sacrificial polymer or hydrogel. Depending on the embodiment, any aqueous media could be used, such as PBS. The duration of immersion is determined by the sacrificial material. In this particular case, the construct was immersed in PBS for 30 minutes at room temperature. It is possible to reduce this time significantly (about 5 min) when immersed at 4° C. Dissolution of the sacrificial layer leads to channels as shown in step 203. While only two channels are shown in FIG. 2, depending on the embodiment that the number of channels could vary.

[0035] The materials and the methods of the present disclosure used in one embodiment for a hydrogel scaffold and device will be described below. While the embodiment discusses the use of specific compounds and materials, it is understood that the present disclosure could employ other suitable materials. Similar quantities or measurements may be substituted without altering the method embodied below.

[0036] Methacrylated hyaluronic acid (MeHA) and alginate (MeAlg) MeHA hydrogels were used as matrix bioinks. These polymers were synthesized as described previously. Ink formulations were prepared by dissolving MeAlg (or MeHA) in PBS at different concentrations in the presence of a photoinitiator, lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP), for blue light crosslinking. A blue light initiator was used as the 3D printer has a built in blue light source. Several ink formulations were developed by varying the MeAlg (or MeHA) concentration. One of the suitable bioink formulations was 9 wt. % MeHA, allowing extrusion based printing of the solution. The present inventors were able to generate struts (individual lines) as small as 100-microns in diameter.

[0037] Pluronic® (F-127), a common sacrificial bioink, was used as a sacrificial hydrogel, to create channels within matrix hydrogels. For this purpose, a dual head bioplotter was used to print the sacrificial and matrix bioink (MeHA) sequentially, as described in FIG. 1. For both matrix materials, the present inventors found that the partial curing time of 10 seconds was sufficient to create self-supporting printed structures. To create channels, sacrificial hydrogel was directly printed within the freshly printed matrix hydrogel layer as described in FIG. 1. After printing was completed, the scaffold was further crosslinked for 4 minutes. The scaffold was then immersed in PBS to dissolve the Pluronic gel. The scaffold was removed from the petri dish, and the PBS in the channels was removed by applying a gentle vacuum. PBS with red food coloring was then injected into each channel using a needle (34- to 27-gauge needle).

[0038] The approach is versatile and enables development of complex channels with tunable shape and size within photocurable hydrogels, either individual or interconnected. FIGS. 3A-3D and FIGS. 4A-4C demonstrate some of the 3D designs and corresponding 3D printed structures.

[0039] As shown in FIGS. 3A-3D a 3D design is accomplished. In particular for this embodiment is CAD designs of the hydrogel scaffolds with channels (light gray: matrix; dark gray: sacrificial). FIGS. 3A-3D are pictorial representations showing the printed scaffolds after removal of the sacrificial regions. FIG. 3A illustrates a plurality of channels with varying channel diameter. Depending on the implementation the diameter of the channels may all be the same or may be varied as represented in this figure. FIG. 3B shows two-layer channel structure where channels are in different planes. FIG. 3C illustrates a plurality of interconnected elliptical channels. Depending on the implementation the channels may be different geometrical shapes or all the same shape. FIG. 3D shows channels forming the logo NJIT. Coarse channels (500 μm in diameter) are printed for visual clarity and easy access with a regular size needle, but 100 μm channels can be printed depending on the embodiment.

[0040] FIGS. 4A-4C show 3D printed structures, and feasibility studies. As shown in FIG. 4A, a schematic of a channel design is illustrated. The channels may follow the same pathway or form various pathways as shown in this figure. FIG. 4B is a top view of an actual sample having the channel design of FIG. 4A. FIG. 4B is a 3D printed construct with Pluronic doped with red food coloring. FIG. 4C illustrates confocal images of the channels in FIG. 4B taken at within the region of the black rectangle in FIG. 4B and perfused with methacrylated rhodamine containing PBS, wherein the channels are smooth and cylindrical in shape with width equal to about 500 μm.

[0041] FIG. 5 is a flow chart illustrating steps of one embodiment of the present method. Shown is one method for making a 3D scaffold. Step 501 illustrates dual printing a matrix material up to a specific thickness for forming a printed layer. Step 502 shows exposing the matrix material to a light source after each printed layer, and partially crosslinking the printed layer to allow self-supporting of the matrix material. As shown in Step 503, printing a sacrificial layer with a sacrificial material directly within an interface layer of the printed matrix material is accomplished. Step 504 illustrates exposing the sacrificial layer to the light source after printing of the sacrificial material. Step 505 illustrates printing a new layer of matrix material. Step 506 shows how repeating the above first through fifth steps (501-505) may be done to create a scaffold in a desired thickness or a human scale. Step 507 illustrates exposing the scaffold to the light source to fully crosslink the scaffold after printing and the desired thickness or the human scale is achieved. In Step 508, it is shown that immersing the scaffold into an aqueous solution is done to remove the sacrificial material for a formation of channels.

[0042] While exemplary embodiments have been described herein, it is expressly noted that these embodiments should not be construed as limiting, but rather that additions and modifications to what is expressly described herein also are included within the scope of the invention. Moreover, it is to be understood that the features of the various embodiments described herein are not mutually exclusive and can exist in various combinations and permutations, even if such combinations or permutations are not made express herein, without departing from the spirit and scope of the invention.