wooden shafts may contain substances that inactivate some viruses and inhibit PCR testing [44] . Thus, the materials used for swab and handle are UV-curable polymer resin and thermoplastic as the former has been tested [45] and the latter does not contact the patient. Many companies and research groups have developed different kinds of swabs [45, 46] . This in itself creates a problem for regulators because of the wide array of designs, materials and printers, many of which are trying to corner specific intellectual property. Callahan et al. have evaluated 160 of swab designs and validated four designs [45] . In addition, a 3-D printed swab consortium has formed [46] . 3-D printed nasopharyngeal swabs have been commercialized from the consortium for proprietary printers from Carbon, FormLabs, Envisiontec, Origin, and Abiogenix. All of the consortium's manufacturers have been verified as ISO13485 facilities and are in production of 'FDA registered' swab designs. The 3-D printer manufacturers have tested and verified the swab designs on their own printers. These designs can be used on other similar printers, but then must be retested and reverified. For example, the company FormLabs has worked with several partners to relatively-openly design and test various materials and geometries of swabs including Beth Israel Deaconess Medical Center [47] , University of Southern Florida [48] , the University of Washington, Stanford University, MIT and the United States Army [49] . Working collaboratively, they have developed test swabs to be printed on high-resolution stereolithography (SLA) 3-D printers and are now being used [50] .2. Hardware description.
As FormLabs printers (and other major SLA 3-D printer manufacturers) are deployed throughout the world they offer a method for distributed manufacturing of nasopharyngeal swabs to help relieve the swab shortage. FormLabs and the other printers in the consortium, however, are proprietary and costly, with a full system costing $3,500-$10,000 for FormLabs as an example [51] . In addition, the swab designs themselves are propriety. For example, the Northwell Swab, that is freely shared now comes with a warning: "This 3D print swab design protocol is patent protected. The University of South Florida grants the recipient of design files permission to 3D print and use the swabs for non-commercial purposes until April 15, 2021 ." [52] . This may cause deployment concerns based on potential liability in the future. In addition, the source, originally available in ref. [52] along with the notice was removed by July 28, 2020.
To overcome these limitations, this study develops a distributed manufacturing solution using only an open source manufacturing tool chain and provides a parametric fully free design of a nasopharyngeal swab. Following well-established open hardware design protocols [28] [29] [30] , the swab was designed using parametric OpenSCAD [53] . This approach has several advantages over the bench mark designs:
1. The front is rounded to reduce the likelihood of injury in the patient's nasal cavity as seen in Figure 1 . The nobs are positioned in an offset sequence so that each row is rotated one nob thickness in the X-Y plane. This is to ensure ideal specimen collection and retention on swab while moving in the nasal cavity. 2. The front and rear of the swab head are tapered to enable easy insertion and extraction of the swab as seen in Figure 2 . The spacing between nobs is selected both for printability and ensuring space for specimen collection. 3. The swab is shortened and fit with a handle. This has several advantages including: i) minimizing print time on relatively slow SLA printers, which increases throughput for any SLA printer, ii) enabling SLA printers with smaller print volumes (like the open source and relatively less costly Prusa SL1 [54] ) to print the swab, iii) reduces the amount of relatively expensive UV resin, and iv) pushes production of the handle over to the more numerous, accessible and faster fused filament fabrication (FFF) over a wide variety of commercial filaments with acceptable mechanical properties [55] or other material extrusion based printers such as fused particle fabrication (FPF) and fused granule fabrication (FGF) [56] . This latter point is perhaps the most important because SLA-based printers are far less numerous than FFF-based printers. Using the two-part design cuts the SLA print time down and allows it to print on small SLA printers, while enabling production rates to be held up with more numerous FFF-based printers used in parallel. 4. The design is fully parametric so any feature can be altered in the future for a specific test, patient, disease or circumstance. For example, as shown in Figure 3 , the handle can be customized with existing test to for example brand it with a specific hospital, State, funder, or company providing the test. Another example is to use different types of handle (see tong handle in Figure 4 ). The press-fit handle minimizes material cost and print time, however, requires pressing the swab base into the handle manually. The tong handle is more expensive in material and print time, however, it distances the user from the swab throughout the entire process. Depending on the tolerances of a specific FFF/FGF/FPF machine the press fit in the handle can be adjusted in the OpenSCAD to work with the SLA printed swab to enable the fit function to work. 5. Mechanical testing on patented 3-D printable swabs showed that they often broke in the neck of the swab when under substantial loads because there was no engineered weak point in the swab. This creates a risk that the swab may break in the patient's nose causing harm and/or being difficult to remove. To ensure that the shaft snaps off in the same location outside of the patient's nose the swab is engineered to fail at a specific location. This is accomplished with a small hole, which can be adjusted in position and radius, located near the transition point from the lower body of the swab to the base section to be put into the handle. The hole is parallel to the press fit bar (see Figure 5 ) so it provides a clear direction to press the body of the nasal swab for it to break consistently. At this point the swab has the least material present per unit cross section and is thus the weakest. [60] . To further cure the resin print head, an open source UV LED box was designed, fabricated and tested. This UV curing box, which is constructed from PCBs, is itself modular so it can be used for UV illumination of other applications.  Swabs can be fabricated 9 min./swab/SLA printer at a cost of $0.014 for the swab head alone and $0.0458 for the swab handle on a FFF machine for a total cost of $0.0603/swab, but perhaps more importantly can be done following a distributed manufacturing paradigm. For context, the traditional manufacturing of a patented single swab is $0.35 with transport medium [61] .  The swab design is two components, both of which can be 3-D printed, although it allows for the slow AM process to be minimized and can be used on small volume SLA printers.  The open source nasal swab design is written in parametric OpenSCAD so other users can personalize it and customize it for their application (e.g. infant/child swabs)  The UV curing system is also parametric and modular enabling the system to be used for any type of UV curing. The LEDs can be swapped out for different wavelengths to be used for other applications (e.g. higher energy UV diodes could be used for virus sterilization). The UV LED type can vary as needed, but for this application 395 nm UV LED's are used [62] . The LED choice is only constrained by the 2.54mm through-hole footprint. [63] . The masses were 0.25, 1.91 and 4.14 grams for the swab, handle and tongs, respectively. The cost of the components was calculated by mass x (cost per unit mass) the cost of the resin is $57.99/kg and the cost of the filament is $23.99/kg. The resin used here is made up of epoxy resin (CAS 61788-87-4, which is a phenolic epoxy resin 40-50%), a monomer (CAS 13048-33-4 which is 1,6-hexanediol diacrylate 20-40%) and photoinitators (CAS 947-19-3, which is 1hydroxycyclohexyl phenyl ketone 3-5%). In addition, resins from Prusa Polymers have a 2-5% color pigment. The swab head is made from the Prusa UV sensitive 3-D printing tough resin and can be purchased in 1-kg bottles online. The swab handle and tongs are both made form Hatchbox PLA filament as tested and printed on a Lulzbot Taz 6. The overall cost of a full swab is $0.0603 with press-fit handle and $0.1138 for the tong style handle.
The UV curing system is parametric in that it consists of modular components which can be linked together to create any size cubic container. As a first step, users can determine the geometry of the curing system with each edge being divisible by 4 inches (since the board has an edge diameter of 4 inches). For this implementation the box is 4"x8"x8". From the dimensions the number of components need can be determined -in this implementation there are 12 boards required.
It is not necessary to solder all screw terminals onto the boards, as they are not all necessary depending on the configuration. To determine where to place the connectors, the boards are laid out in their "unfolded" state, as seen in Figure 7 , and terminal block pairs are places such that power can be supplied to each board at least once. Redundant connections will not hurt the system.
The boards have provisions for resistors if it is determined that the light intensity needs decreased, but for this application max intensity is desired. In this case, 0 Ohm resistors can be soldered in place, or to cut costs further, the clippings from the UV LEDs can be used to bridge the two pads. The UV LED soldering requires no special treatment -aside from the fact that LEDs are polar and therefore must be soldered in the proper orientation. The LEDs should be soldered on the opposite side of the silkscreen such that they will be facing the interior of the box. Figure 7 . The UV curing box is first laid out in order to determine terminal block placement.
If cost is a major concern, the terminal blocks can be replaced with directly soldered wire as seen in Figure 8 . This is undesirable in most cases as it reduces the maintainability of the system (i.e. it can not be as easily disassembled as it would need to be de-soldered). Once the boards have been fully soldered, the next step is to identify boards that are on the same plane -specifically terminal blocks that are intended to be connected to one another. Since they are butted up end to end, placing typical wire in the connectors is not an option. Instead, solid resistor leads are cut to the correct length and clamped in place ( Figure 9 ). At this point, the necessary brackets can be printed, and the boards can be bound together. The M3 bolts can be applied two ways -they can either be fed through the exterior of the box and then terminated with a nut, or in the case of this application, the bolts are fed through the interior and thread directly into the plastic. No nuts are necessary.
Next, the corner joints can be wired using any standard insulated wire ( Figure 10 ). Two lengths of wire can also be tapped into one of the screw terminal sets ( Figure 11 ) and wired to their respective plus and minus terminals on the power supply. The IEC power cable can have its end cut and stripped. Though the color key may vary, typically the green wire will connect to the ground terminal of the supply, the lightest color will tie to the neutral terminal, and the darkest color will tie to the live terminal. This wiring color scheme should be verified on a case by case basis. Figure 11 . Two cables tapped into a terminal set for power flow from the supply Before powering on the completed box ( Figure 12 ), a multimeter should be used to measure the input resistance of the box, if it is a low number (around 5 or less Ohms), there is likely a short. Fabricators should double check each connection point and verify there are no loose strands of wire. Once the box is short free, it can be plugged in, and its functionality can be verified. It is important to point out that the LEDs are directional and will seem dimmer when viewed from the side ( Figure 13 ). 
In order to begin printing on the Prusa SL1 printer, it must be calibrated. Figure 15 shows the Recalibration Screen. [64] and is used to import the nasal swab STL file onto the build plate. The design should be multiplied as many times as possible while ensuring a fit on the build plate ( Figure 16 ). Prints were tested in a 5 by 10 array printing 50 swabs simultaneously.
When the nasal swab design was sliced, an estimated 13.69 mL of the resin was used. This build plate design was exported onto a flash drive that can be inserted into the Prusa to print. The Prusa will load a screen for how much resin must be in the tank in order to fulfill the requirements for the print ( Figure 17 ).
The print layer is set to 0.05 mm where the first layer was attached with UV light for 35 seconds and every consecutive layer was attached for 7 seconds. The estimated print time for this sequence is 6 hours 53 minutes. This does not include calibration of the printer (which is approximately 5 minutes) and mixing of the resin once the print begins. Once the print is done, excess resin should be allowed to drip off. After printing, the swabs are removed from the print bed and cleaned with 90% or higher isopropanol and dried by lying flat on a sheet of paper towel ( Figure 18 ). Each swab was individually rinsed with a squirt bottle while also checking on resolution of the swab head ( Figure 19 ). This process takes approximately 20 min. The cleaned nasal swabs can either be placed directly in the UV curer or placed on a paper towel to dry. Leftover resin in the basin can be poured into a UV-blocking container, such as a metal water bottle, to be reused once it is filtered. The basin can then be carefully cleaned with paper towel. Warm water and soap can be used to ensure that the film is clean and clear, but metal or isopropanol should not be used to clean the film of the basin. The cleaning process takes approximately 20-30 minutes. Figure 20A for an individual press-fit handle and batches of 45 handles are shown in 20B and 20C for the tong and press-fit design respectively. It should be noted that the range of acceptable parameters for the FFF-based 3-D printing for the handle is large and will vary for a given open source 3-D printer, but that the handle is not particularly critical as long as the swab fits well. These parameter changes work for both print materials and both handle versions. A precise outer surface is critical for a clean connection between the press-fit handle and the base section of the nasal swab. The tong handle also benefits from a precise outer surface to both clamp the base of the swab securely and minimize unintended tolerances. Print settings which lower the resolution may lead to a poor fit and inhibit effective use of the swab. In this work, PLA and PETG of multiple colors and brands were used and printed at suggested temperatures by Cura-Lulzbot normal settings. A printed handle post-print is shown in Figure 21 . The swab inserted into a tong handle is shown in Figure 22 . A Lulzbot Taz 6 printer holds 45 press-fit handles, which takes 7 hours and 19 minutes to print. Similarly, on the same print bed 45 tong handles and takes 14 hours and 39 minutes to print. More handles could be fit on the print bed, but these values were chosen to match the SLA printed batches, which would be the limiting factor. Similarly, even more handles could be made in a single print if they were stacked, but based on the print time for 45 this may cause a higher percentage of print failure while adding only modestly to the convenience. 
It is well known that the FFF printing process produces sterile objects [66] because of the high temperatures for material extrusion, so if care is taken to chemically sterilize the print bed and use sterile gloves, the handles can be sterile at manufacture. In addition, the chemical compatibility of most commercial 3-D printing filaments has been investigated by Heikkinen et al. [67] , which can be used to find an appropriate chemical for any handle material. The swab itself is fabricated using sterile UV light, the post print cleaning is done with isopropyl alcohol that is a disinfection agent and then cured in UV light. Thus, if appropriately handled the swab can remain sterile. Depending on the fabrication facilities and handling the assembled swab and handle may need to be sterilized. The swabs and handles can be sterilized on site and packaged at fabrication or at the hospital. The sterilization should be a non-autoclave process because of the risk of thermal degradation. For example, this can be done with hydrogen peroxide (e.g. the STERRAD process (www.asp.com), which uses hydrogen peroxide vapor and low-temperature gas plasma to sterilize quickly with no toxic residues). The sterilized swabs can be individually packaged in heat sealed plastic pouches, although this was not included in the economic analysis.
The open source UV curing system being used is made from LEDs and circuit boards and is attached to a 12-volt power supply. The swabs are placed in a 3-D printed holder hanging tip down and placed in the UV curing box and the lid is closed over them ( Figure 14) . The box is plugged in and a timer is set for 45 minutes. Remove swab head from packaging with gloved hands and attach handle as shown in Figure 23 if it is not already assembled. Figure 24 . Using the open source nasopharyngeal swab and press-fit handle.
After removing from packaging and if needed, assembling, insert the semi-flexible open source swab through the nares parallel to the palate (not upwards) as shown in Figure 24 until 1) resistance is encountered indicating contact with the nasopharynx or 2) the distance is equivalent to that from the ear to the nostril of the patient [44] . This area is sensitive so care should be taken. At this location shown in Figure 24 gently rub the swab and leave it in place for several seconds to absorb secretions. Then, while rotating the swab slowly remove it. After extracting sample following Figure 24 , break off tip of swab and place swab immediately into sterile tubes containing 2-3 mL of viral transport media [44] . See [44] for guidance on storage and shipping samples.
To validate the open source swab, 100 swabs were printed on a Prusa SL1 and underwent the following preclinical testing. The open source nasopharyngeal swabs were mechanically tested for tensile strength, break point and rotation angle at failure and compared to proprietary FormLabs printed nasopharyngeal swabs. The open source nasopharyngeal swabs were also tested for absorption, abrasion and handling testing.
Tensile tests were performed on the open source swabs for four different UV curing times: 10 min, 20 min, 30 min and 45 min. Optimum curing times were selected based on the average load during break and standard deviation for 5 specimens. The optimum curing time was then used to cure an array of swabs. 5 specimens were then chosen randomly from the array to test for average load during break and standard deviation. FormLabs samples were also tested for comparison. Tensile testing is meant to mimic pulling the swab out of the nasopharyngeal space. The average load at breaking for the samples at various UV curing times are shown in the Figure  26 . The highest load at break (40.97N) was at a curing time of 45 min, which was only a slight improvement on the 30 min. cure time and within error of the 30 min cure. This indicates that complete curing has taken place and was thus used throughout the remainder of the testing. It should be noted that all of these forces (40N is about 4 kg of force) are significantly more than would be expected in a clinical application. Although, the open source swabs had a lower tensile strength than the FormLabs swabs, this was purposefully engineered into the design to ensure that the swabs would not break inside of a patient's nasopharyngeal space. All the Form Labs specimens broke around the middle of the swab. If this were to occur in a patient this would create a new medical problem. All open source swab specimens for all curing times broke at the neck near the handle as designed (hole shown in Figure 5) . Representative examples of this can be seen in Figure 27 .
The position of the swabs in the UV curing box was shown not to be a significant factor in the strength. The specimens chosen from the array of swabs cured at 45min broke at an average load of 38.02N with a standard deviation of 5.14N.
The open source swabs were also tested for rotation until break by placing one end in a vice and rotating. The swabs broke at the break point after about 360 degrees of rotation, which again is far more than would be expected for clinical applications. 
Three different tests were conducted on the open source nasal swabs that were cured for 30 minutes on each side. The first test was with synthetic nasal mucous (Kryolan, Cotati, CA) [68] . The dry swab was weighed on a calibrated open source digital scale [63] . Then, the swab was placed vertically in synthetic nasal mucous and massed again. Then, the excess nasal mucous is gently rubbed off on paper towel and weighed again in order to determine how much is stored within the tip of the swab when inserted into the nasopharynx. The second test was to capture the nasal mucous by putting it in a petri dish and twisting the swab in a rotational manner. Finally, the third test was done with a honey-water (3:1) mixture that approximated the viscosity of the synthetic nasal mucous so that those developing other swab designs can use more readily available materials (at the time of this writing there was only one synthetic nasal mucous supplier in the U.S.). All experiments were repeated five times.
For the twisting petri dish tests the swabs were found to hold 0.306g (SD 0.014). For the swabs dipped vertically the swabs held 0.304g (SD 0.016). These values were found to be comparable with the commercialized FormLabs swabs with an average of 0.297g. These results indicate that the open source swabs printed on a Prusa SL1 can absorb an adequate amount of material to be used for testing.
The 3:1 honey mixture provided similar results with a mass held between the rough surface of the tip to be 0.314g (SD 0.023). Although the spread in values was slightly higher with the 3:1 honey mixture these results indicate future swab designers can use honey and water to test absorption in new swabs.
Overall it was found that approximately 0.068g of material gets caught within the tip of the nasal swab after lightly rolling the swab over a piece of paper towel after dipping in synthetic mucous.
Tip abrasion tests were performed by 1) massing the dry weight of the swab on the open source digital scale [63] , 2) placing distal end of swab (absorbent end) next to human tissue (inner left arm) and applying a rotation to proximal end (hand side -handle) at hand twirling speed for 10 seconds, and 3) the swab was removed wash and dried, and 4) massed. The difference in the pre and post abrasion test was recorded. Each experiment was repeated for five trials.
There was no change in mass within error indicating the tips were rugged enough for this application as the arm skin is rougher than that of the inner nasal passage.
Following Callahan et al., [45] the swab heads were tested for head and neck flexibility and robustness to fracture (Figure 28 ), robustness to repeat insertion into and removal from a tortuous canal (diameter ~3.50 mm (Figure 29 ). The neck bending occurred by holding the swab above the break point and bending it to the swab's nose. Swabs could bend 180 degrees as shown in Figure 28 . For the robustness to repeated insertions into and removal from a tortuous canal test the tip of the nasal swab was inserted and removed into a 3-D printed channel (https://osf.io/t6yqk/). During both insertion and removal, the swab was rotated slightly by hand as shown in Figure 29 . This process was repeated 20 times. As an end result, there was no visible damage to the swab. Note that the swab needs to be held by the neck past the point where there is an engineered weakness. Finally, it should be stressed that the swab heads broke at the designed weak point near the insertion point of the handle Figure 27 ). The engineered break point can be an issue for the selection of handle type if the swabs are improperly handled. To work the press-fit as designed the swab needs to be pushed into the handle at the T, if not (e.g. pushed from above the break point) it can break at the break at the designed break point point. Open source swab manufacturers may need to adjust the print parameters or design slightly to get a reliable press-fit on their specific FFF/FGF/FPF machine because of varying print tolerances. All of the variables are defined and are adjustable in the OpenSCAD. Minimum angle of fragments and sizes are set at 0.5 and 0.15 respectively with recommendations about changing these variables in the code. Material extrusion users can use standard approaches to fixing either an under or over extrusion that is preventing a good press fit (e.g. recalibrating or adjusting the temperature of their printer). On the other hand, the tongs are more easily fabricated. The tongs are also easy to use, do not require more work on the user's part, allow the swabber's fingers to be further from the swabbee's nose, and make it easy just to drop into viral transport media (VTM). The tongs do have negatives of being costlier and twice as time consuming to produce (because of print time on the FFF/FPF printers) as compared to the press-fit handle. There are some opportunities to reduce this cost by redesigning to be thinner, printing at a lower fill density or shell thickness, but for any given set of print parameters they need a larger volume of material than the press-fit design.
Standard safety procedures should be used for FFF-based 3-D printers [69] . For the UV 3-D printers, the casing on the printer must be closed when the print is in progress as exposure to UV light can cause premature skin aging and mutations or eye problems [70] . When using isopropanol to wash the prints, users should wear gloves and eye protective gear [71] . The gloves will protect from possible burning or irritation of the skin. It is flammable, so keep away from flames and high heat.
Nasopharyngeal swabs, which are used to collect specimens from a patient, are Class I devices and are 510(k) exempt [72] from premarket notifications in the U.S. according to 21 CFR § 880.6025 [73] . For the FDA, as of this writing (5-6-2020) 3-D printed swabs are a new technical area that the FDA is working out guidance. Traditional swabs are 510(k) exempt and as such are not generally reviewed by the FDA [74] .
Fabricators should check with their local laws, however, as for example the U.S. Food and Drug Administration (FDA) requires medical device manufacturers to register their facility and list their products according to 21 CFR § 807.20 [75] . As of this writing (5-6-2020) this is challenging in the U.S. because the rules differ by state. For example, the Michigan Health Association is running studies with clinical labs across the state [76] . Some public health entities are testing specific safety issues related to some 3-D printed materials. The 3-D printing materials used in this study have not yet been approved of for biological applications and future work is needed to ensure the resin used on the tip is compatible with the human nasopharynx. In addition, although the basic makeup of the resin for the tip and hard plastics for the handle used here were known, the pigments and any other additives was not disclosed. This problem has been discussed before [77] in the context of expanding John F. Kennedy's Consumer Bill of Rights to include material ingredients [78] . This application of distributed manufacturing using 3-D printing for critical medical devices during a pandemic [79] further underscores the necessity to have all materials be openly available and disclosed for all products, but particularly for those used in manufacturing.
In addition, as the results here clearly showed that after post-printing uv curing, the mechanical properties of the swabs improve. This means that there are mobile chemicals and monomers within the printed structure that have the potential to irritate human tissue as the uncured material can be harmful as a respiratory irritant [80] . Future work is needed to verify the presence of free monomers or chemicals to indicate for how long they can be extracted out while immersed in IPA. Similarly, this design with a FFF/FPF/FGF printed handle was made without an intension of reuse. This is because the ability to sterilize material extrusion parts is limited because of their low melting temperatures of often used feedstocks (e.g. PLA, ABS, PETG) restricts the use of thermal sterilization. Sterilization is possible with autoclave, ethylene oxide, hydrogen peroxide and gamma radiation; although the former causes major deformation and the others present challenges [81] . 3-D printed materials can be compatible with H 2 O 2 vapor sterilization, but again there are substantial challenges [82] . Another approach is to use an open source high-temperature printer to fabricate the handles in polyetherketoneketone (PEKK) or polyetherimide (PEI, ULTEM), which would allow for thermal sterilization [83] . Although the open source printer can be manufactured for $1,000 in parts it is new and other high-temperature material extrusion printers are high cost and thus also not as well-dispersed as standard desktop FFF-based machines.
These biological compatibility experiments are needed to show the safety of the 3-D printing materials before this approach can be used clinically. As NP swabs fall under a specific device class, the FDA has a running list online of specific manufacturers and types of materials acceptable for use in COVID responses. This presents a challenge to distributed manufacturers. Currently, Michigan MDHHS, BOL have been using the list for what they can use. It is up to each and every lab director to make their own decisions and turn in appropriate paperwork documentation to FDA regarding what they choose to use based on how it fits with their assay EUA documents (some platforms have more restrictions than others) [76] . This obviously provides a bureaucratic barrier to acting quickly, which in part explains the limited supply of swabs in Michigan. This work should help expedite distributed manufacture of nasal swab use for future pandemics or supply disruptions.
A nasal swab goes into the nose about 4-6 cm from the nasal opening to the back of the nasopharynx. A good rule of thumb is the distance from the opening of the nose to the opening of the ear (measured on the outside). Commercial swabs have a relatively firm 10.5 cm long handle that is approximate 2.5 mm diameter. This attaches to a flexible 3.5 cm in length neck 1 mm diameter, where the break point is. This in turn is attached to the fibrillar head, which is 2.0 cm in length, with an approximate 3 mm diameter. The variance in the SLA prints is not a factor in this application (e.g. the diameter of the head).The proprietary 3-D printed swab tested (the Northwell Swab STL) with the base handle cut off (97%) is approximately 97.15 mm. The total length of the swab would therefore be about 100 mm (100.0645 mm). The final dimensions of the open source swab are: length of 85.20 mm, diameter at the base is 2.45 mm, length of the neck is 54.60 mm with a 1.05 mm diameter and length of the head is 22.30 mm with a diameter of 3.30 mm. Both the tong and press-fit handles are 80 mm in length, creating a total for the new swab and handle to be approximately 156.57mm since the base of the swab is held in the handle. The open source design provided here is able to meet these specifications with a broad flexibility of using the parametric design to meet different types of swab needs.
The results of the mechanical validation tests showed that the swabs could withstand greater forces than would be expected in normal clinical use. The swabs were also able to absorb a significant amount of material and passed the abrasion and handling tests. The open source swab therefore appears to be a promising candidate for clinical trials.
The single swab stl can be copied until an entire print bed is filled in the PrusaSlicr Program. In this study, the Prusa print bed was organized in a 5x10 swab fashion (50 swabs per print), to allow each swab build space towards the fibular tip. Future work could evaluate printing the swabs at a higher density and filling the entire build platform. At the same time, the quality of a particular print is important for this application so a low-cost rapid method of quality verification can be developed as future work as well.
The bottle neck SLA 3-D print time for the open source swab is 6 hours 45 minutes for 50 swabs. For the entire process from calibration to cleaning of the swabs, is approximately 7.5 hours. So, the throughput of the SLA portion of the swab represents about 9 min/swab/machine. The ability to use lower cost UV curable resin from Prusa or other open materials suppliers also represents potential cost savings compared to proprietary SLA systems although future work on the yields of those systems would need to be completed for a full cost comparison. As there is significant time and cost savings using a two-part design the economics for other SLA printers would improve for printing swabs if a similar design to the one shown here is used.
Another distinct advantage to this two-part system is the ability to brand or customize the handle. This feature could be used to cut down on waste. Normally swabs are discarded as medical waste and incinerated. As only the head of the open source swab goes to the lab for testing the handles could be either sterilized and reused as handles or sterilized and reused for other applications. An example might be to make a handle with Lego compatible geometries so that sterilized swab handles could be cleaned and then used in children's waiting rooms at the hospital as building blocks.
This design is fully licensed as open source (as defined by the Open Source Hardware Association (OSHWA) [29] ), which comes with distinct benefits for scaled distributed manufacturing as well as enabling creativity and productivity in the case of future pandemics or needs. In general, the designs in clinical use are proprietary and provided with a license waiver on a high-cost proprietary tool. This provides the opportunity for some emergency distributed manufacturing, but it is limited, mostly by access to the high-cost tooling. There are freely available (accessible) untested designs that are creative commons licensed with a noncommercial license (for example see untested accessible designs [84] [85] [86] [87] ). These designs are thus not strictly open source by the OSHWA definition as they restrict manufacturers from selling them, which could limit deployment as for example distributed manufacturers would not be able to recoup the cost of materials or their personnel time.
Lastly, and most importantly the open source swabs need to be verified clinically before widespread use. The State of Michigan has a Validation Plan [88] , which includes a 3-D Printed Swab Bridging Study. To bridge the performance of novel 3-D printed swabs, the FDA recommends [89] testing 3-fold serial dilutions of SARS-CoV-2 viral material in pooled respiratory sample matrix in triplicate in parallel between the new and existing component, where the smallest serial dilution should be no greater than 1-2X the demonstrated limit of detection of the assay. According to the FDA, acceptance criteria is 95% concordance between the two components. In Michigan each laboratory will determine the parameters to evaluate to assess agreement based on the technical performance of their assays. These tests will need to be completed for the open source nasopharyngeal swabs for the specific UV-curable materials used. 3-D printer operators can work with clinicians to assess suitability of prospective products for use in local patient care settings.