Mobile phone microscopes are a natural platform for point-of-care imaging, but current solutions require an externally powered illumination source, thereby adding bulk and cost. We present a mobile phone microscope that uses the internal flash or sunlight as the illumination source, thereby reducing complexity whilst maintaining functionality and performance. The microscope is capable of both brightfield and darkfield imaging modes, enabling microscopic visualisation of samples ranging from plant to mammalian cells. We describe the microscope design principles, assembly process, and demonstrate its imaging capabilities through the visualisation of unlabelled cell nuclei to observing the motility of cattle sperm and zooplankton.
The rapid advancements in imaging capabilities of consumer mobile phones over the last decade have made such devices attractive for point-of-care and resource-poor microscopy applications. Microscopy-enabled mobile phones have been used for a variety of purposes including malaria diagnosis1, sperm tracking2,3,4 and water quality assessment5. These mobile phone microscopes come in a variety of form factors with a range of working principles. An early design was comprised of a standard microscope objective interfaced to the mobile phone camera via a lens tube and eyepiece6; a later iteration more resembles a miniaturised benchtop microscope, with a 3D printed stage and chassis7. A simpler, lower resolution mobile phone microscope consists of an additional camera lens along with the integrated camera lens to form a unity magnification imaging system8,9,10. Together with an external light emitting diode (LED) and stage, this forms a transmission mode brightfield microscope, with enough magnification to image red blood cells. This basic optical design consisting of a magnifying lens and an external LED also forms the basis of the ultra-low-cost Foldscope, made primarily from origami paper11.
Another class of mobile phone microscopes are lens-free devices that image via holography2,5,12. With these devices, the sample is placed directly onto the image sensor. The sample is then illuminated by an external light source in a particular geometry so as to create a series of holograms, which are captured by the image sensor. Subsequent image processing translates the raw holograms into images. Advantages of this approach are increased resolution and light collection efficiency since there is no lens to limit the numerical aperture. Lens-free techniques are also amenable to tracking in 3D since the holograms carry 3D information. However, the image is not viewable in real-time and often requires processing on a powerful desktop computer or in the cloud. More importantly, the user must disassemble the camera module itself to remove the lens and place the sample directly on the image sensor. Cleaning the sensor after use is also not practical. These challenges are a hurdle for wide scale adoption of lens-free mobile phone techniques.
Despite the assertion that mobile phone microscopes are simple, low-cost tools for use outside the lab, most mobile phone microscopes require extra components, most notably external illumination modules. Three published exceptions are a lens-free device that uses the sun as an illumination source5, a brief report that describes the use of diffuse reflection from a slide holder placed behind a sample9, and an immunoassay device that uses a mirror and optical window to steer light from the flash towards the sample13. Aside from these three publications, every mobile phone microscope described in the literature features an externally powered LED light source. External LEDs and batteries add extra bulk and assembly complexity to a system that is meant to be as compact and simple as possible. Ideally, a mobile phone microscope would take advantage of the integrated flash found in nearly every modern mobile phone, obviating the need for external lighting and power. Practical pitfalls such as sourcing replacement batteries and the potential for water damage to the illumination electronics are also avoided by using the internal flash. The difficulty in using the built-in camera phone flash is that the flash is offset from the camera by typically a few mm, and is pointing in the same direction as the camera.
Reflection mode microscopy is not possible in this configuration since the flash does not illuminate a sample located near the camera’s entrance aperture; transmission illumination mode is also not possible as it requires the light source and camera to be on opposite sides of the sample along the optical axis. Using the integrated flash of the microscope appears to require additional mirrors and lenses to turn and condense the illumination light back onto the sample13. This, in turn, would necessitate additional optical components (adding cost and bulk), and consequently would defeat the purpose of using the internal flash.
In this work, we describe a 3D printed microscope add-on clip that enables transmission brightfield and darkfield microscopy on a mobile phone without any externally powered light source or additional illumination optics. For brightfield transmission mode, our design takes advantage of the integrated phone flash together with diffuse reflection in a similar manner to that previously noted9. Unlike in this previous report, our 3D printed device itself has the necessary geometry to create diffuse transmission illumination without employing an external diffusely reflective object behind the sample. Moreover, darkfield imaging is made possible by designing the clip so that ambient light only can illuminate the sample via internal reflection within the sample glass slide. As a result, we can observe samples that are nearly invisible under brightfield operation due to low absorption or refractive index contrast, such as cells in media.
Because our design requires no external power or light sources, it is particularly robust, making it ideal for use in remote areas and fieldwork. Our microscope requires only a single assembly step (inserting the lens into the 3D printed clip), avoiding more complicated assembly involving electrical hardware and multiple 3D printed parts. The simplicity not only makes it easy to set up and use but also helps to drive down cost when assembly costs are taken into account.
In this paper, we outline the design and operational principles of our mobile phone microscope followed by optical characterisation and application examples. We have also made the Solidworks and STL files for 3D printing freely available to enable users around the world to print their own microscope clip.
Materials and Methods
Microscope clip design
Our mobile phone microscope design consists of a 1x magnification imaging system that is created by placing a mobile phone camera lens (exterior to the mobile phone) in front of the mobile phone’s existing internal mobile phone camera module8. This configuration resembles a classic infinite-conjugate microscope design that is the basis of modern optical microscopes14. The exterior mobile phone camera lens is friction-fit into a recess of the clip (“lens” in Fig. 1a) and plays the role of the objective lens, while the camera lens inside the phone takes on the role of the tube lens. If the sample is placed one focal length in front of the objective lens, an image is formed one focal length behind the tube lens. Mobile phones are designed to image near infinity by default, meaning that the standard position of the image sensor is typically one focal length behind the tube lens. In such an infinite conjugate system, the optical magnification is the ratio of the focal length of the objective to tube lens – 1x in our case. However, because the pixel size of mobile phone cameras is so small (1.22 μm for iPhone 6 s), 1x magnification nevertheless results in microscopic resolution. As noted previously, the advantage of using a mobile phone camera lens as the objective is that these lenses are very well corrected for aberrations, thus yielding images far superior to those captured with a more simple optic such as a ball lens8. Moreover, due to mass manufacturing, mobile phone camera lenses are inexpensive, especially given that they have multiple lens elements. One can extract the camera lens from an iPhone camera module purchased online for $15 AUD15. This cost can be further reduced by purchasing camera lenses themselves in bulk direct from the manufacturer.
The novelty of our device lies in the illumination design. Instead of employing an external LED, we use the internal mobile phone flash. To use the flash in transmission geometry, we design a microscope clip with internal illumination tunnels, as shown in Fig. 1. The entrance of the tunnel is placed at over the camera flash. Light from the camera flash travels through the first tunnel (blue in Fig. 1a-c), reflects diffusely off of the end of the tunnel (gold in Fig. 1d) and then travels back into another tunnel that is aligned to the optical axis of the objective lens and camera module (green in Fig. 1a-c). The end of the tunnel is made of the same cured resin as the rest of the microscope clip – the entire piece is a single monolithic printed object. After being diffusely reflected, light from the camera flash illuminates the sample in transmission (green arrows in Fig. 1c). A similar approach has been used to trans-illuminate samples in endoscopy, where one does not have access to the rear of the sample16. For our device, we estimate the sample illumination intensity by shining the iPhone flash through each portion of the illumination tunnel and measuring the output power with a digital power meter (Thorlabs S130C). Of the initial 45 mW emitted by the iPhone flash, 2 μW (9.2 uW/cm2) reaches the sample plane. Though the attenuation is substantial, it helps to avoid saturating the iPhone camera sensor. For comparison, we measured an illumination intensity of 2.8 μW/cm2 for a detector placed 1 m in front of the iPhone flash, with no obstructing objects in between. Thus, despite losses from reflections within the illumination tunnel, the illumination intensity is still comparable to what is achieved by the flash under normal flash photography conditions. This is perhaps unsurprising considering that the camera LED is designed to illuminate objects at distances much larger (>1 m) than the path length in our microscope (~1 cm).
Another convenient feature of this approach is that the illumination results from a diffuse reflection. Ideally, brightfield transmission microscopy is performed with Kohler illumination17, where light travelling in all possible angles admitted by the numerical aperture (NA) of the condenser hits every point in the sample. Despite the lack of a condenser lens, our geometry approaches this condition because diffuse reflections create light travelling in all directions. In our microscope clip, the effective illumination NA (0.23) is defined by the area over which the diffuse reflection occurs (a circle of radius 2.63 mm) and the distance between where the diffuse reflection occurs (resin back stop, coloured gold in Fig. 1a,d) and the sample (11 mm). This illumination NA matches the NA of the imaging objective (f/2.2), just as in a standard brightfield microscope.
When operating the mobile phone microscope, the user can choose to turn the flash on or off. Turning the flash on results in a transmission brightfield image as described. However, with adequate ambient lighting, an image is still created when the flash is off, despite the lack of direct sample illumination. This image is the result of light trapped via internal reflection in the microscope slide being scattered into the objective lens by the sample. In this configuration, light cannot land on the image sensor unless it is scattered by the sample, resulting in a dark background18. Darkfield imaging modalities such as this are particularly useful for observing samples that do not absorb strongly or that are nearly index matched to their surroundings.
Fabrication and assembly
We print our microscope clip using a Formlabs Form 1 3D printer. The microscope clip design file is converted from STL to the native Formlabs format and then uploaded to the printer via the standard PreForm software. For an acceptable contrast in darkfield mode, it is necessary for the microscope clip itself to be opaque. As a result, we print the microscope clip in black resin (Formlabs GPBK02). Printing in white or grey resin severely degrades darkfield imaging performance. For optimal print speed, we print without supports, with the clip oriented on its side (so that it takes on an “L-shape” then viewed from above) and select a layer thickness of 0.1 mm. Printed clips are then rinsed in IPA as per the suggested Formlabs protocol19. After rinsing, the microscope clip is let to dry and is then put under sunlight for 1–2 hours to post-cure (post-cure optional).
After drying and post-curing, the objective lens must be inserted into the microscope clip. The objective lens fits into a rectangular recess designed to hold the lens in place via friction. The objective lens is inserted into the clip from the front as shown in Fig. 2a–d. Squeezing the microscope slide holder sets the objective lens into place at approximately the right position. If needed, the objective lens position can be adjusted by pushing it further into the recess using tweezers. Note that the objective lens should be oriented in the opposite direction to the internal camera (tube) lens. That is, the surface of the objective lens that was previously facing the sensor should be facing the sample.
Once the objective lens is in place, the clip is fitted over the mobile phone such that the objective lens is directly over the internal camera module (Fig. 2e). Samples mounted on microscope slides can be inserted into the clip as shown in Fig. 2e. Though we did not encounter any contamination of the lens with overflowing sample liquid, if at any point the lens becomes contaminated with debris, the lens can be pushed out gently with tweezers and wiped with lens tissue dipped in isopropyl alcohol.
The native iPhone camera app enables either brightfield (with flash on) or dark field imaging (flash off). An example of a brightfield image of a Lilium ovary (Southern Biological) acquired with the microscope is shown in Fig. 2f. Although the native iPhone camera app sets the camera gain (ISO setting), exposure time and focus automatically, third-party apps are freely available that enable manual tuning of these parameters20. In our experience, the automatic adjustments made by the native iPhone camera app were adequate for routine imaging. Though the image was not always initially in focus when the native iPhone camera app was started, the touch-based auto focusing mechanism was sufficient to find the correct focus plane.
Results and Discussion
The optical magnification of the mobile phone microscope is equal to the ratio between the focal length of the lenses. We use an iPhone 5s back camera lens paired with the internal iPhone 6s back camera lens, which both have an f/2.2 and focal length 4.15 mm, giving 1x optical magnification. The pixels on the iPhone 6s camera are on a 1.22 μm pitch, suggesting a Nyquist-limited resolution of 2.44 μm. However, the colour Bayer filter together with the camera’s internal demosaicing reduces the achievable resolution because only one colour is sampled per pixel. Though the optical magnification is fixed at 1x, the digital zoom and imaging mode of the iPhone affects the apparent pixel size. At native 1x digital zoom in “Photo” mode of the native iPhone camera app, we measure an effective pixel size of 1.22 μm, as expected. At full digital zoom in “Photo” mode, the effective pixel size is reduced five-fold to 0.24 μm via automatic software interpolation by the iPhone. In “Video” mode, pixel sizes were measured to be 2.19 μm and 0.73 μm at 1x and 3x digital zoom, respectively. Note that at 1x digital zoom in “Video” mode, the iPhone undersamples the image sensor, making it necessary to use digital zoom to maintain full spatial resolution.
We measure the microscope resolution by imaging USAF-1951 resolution targets. For a given resolution target element to be considered resolvable, we required that the average grating contrast for both x- and y-orientations exceeds 10%. We define the average grating contrast as the average of (Imax − Imin)/(Imax + Imin), where Imax is intensity of the grating line (or space between grating lines for the phase target in brightfield), and Imin is the intensity minimum between each grating line (or intensity of the grating line for the phase target in brightfield). Focus was achieved by using the touch-activated autofocusing mechanism of the native iPhone app, focused on the smallest resolution group visible. We employ two types of targets, one consisting of 2 μm thick photoresist (Nanoscribe IP-Dip) features on a quartz slide (phase target, Fig. 3a,c), the other with transparent features on a chrome-coated glass slide (chrome target, Fig. 3b). Transparent objects, such as the photoresist features on the phase target are sometimes harder to resolve than opaque features, as they do not produce as much intensity contrast. Despite this expectation, we find that the smallest resolvable elements of both the chrome and phase targets are essentially equal, at 4.48 μm (15.59% contrast) and 4.38 μm (11.65% contrast), respectively. In darkfield, the phase target is easily visible under ambient room light. The resolution, however, is slightly worse than in brightfield mode, with the smallest resolvable grating having a pitch of 5.60 μm (12.16% contrast). Intensity traces for the smallest resolvable resolution element for each target type are shown in Fig. 3d. These resolutions were found to be fully reproducible for each test target, using the iPhone autofocusing feature. If the autofocusing feature is not adequate for finding focus in more complex samples, users are encouraged to use 3rd party camera apps that enable manual control of the focus position20.
Improved optical resolution could be achieved by using a shorter focal length objective lens. For example, the front camera lenses on smartphones typically have focal lengths in the range of 2–3 mm, which could improve resolution up to two-fold over the 1x magnification system presented here. Even shorter length ball lenses or microlenses21 are of potential interest, though these elements have significant field aberrations4,11.
The advantage of using darkfield illumination becomes apparent when imaging transparent objects such as cells in a nearly index-matching medium such as water. In brightfield transmission, the refractive index contrast within the cell and between the cell and its surroundings produces almost no intensity contrast. In darkfield, however, the illumination light is mostly trapped inside the glass slide, mounting medium and coverslip, and can only be collected by the objective lens if scattered. This leads to a dark background with bright features, which is the ideal situation for observing minimally absorbing, nearly index matched objects. The brightfield transmission image of a Caco-2 cell culture is shown in Fig. 4a,c. The cells are hardly visible due to low contrast, and it is unclear how many cells are present. Towards the edge of the field-of-view (FOV), where the effective illumination NA is lower, cells become visible due to asymmetric illumination, but barely so before the signal drops off significantly due to vignetting. This vignetting restricts the illuminated field of view to a circle with full width at half maximum of 1.6 mm. A striking improvement in contrast and reduction in vignetting is seen in the darkfield image of the same FOV (Fig. 4b).
Though the cells are nearly invisible under brightfield illumination, the darkfield image shows that the cell culture is in fact highly confluent. A careful comparison between Fig. 4c,d indicates that only the very strongly scattering cells that saturate the camera detector in darkfield produce enough contrast to be visible in brightfield. Not only are unlabelled cells visible in darkfield, but cell nuclei are clearly visible in a magnified view of a region of the FOV (Fig. 4d). The cell cytoplasm appears brighter than the nucleus likely because of all of the fine cellular features inside the cytoplasm acting as scattering centres. Using a custom MATLAB script22, we show that the contrast between the nuclei, cytoplasm and the surrounding background is enough to enable basic cell counting, without resorting to fluorescent dyes or histopathology stains.
Dynamic samples can be observed with the mobile phone microscope using the “Video” setting on the native iPhone 6 s camera app. We test the feasibility of live cattle sperm quality assessment both in brightfield and darkfield modes on our mobile phone microscope. In brightfield, dark-oval shaped spots corresponding to the sperm heads are visible. Figure 5a shows the first frame of a 21-second movie (Supplemental Movie 1) of cattle sperm swimming freely between a microscope slide and coverslip, recorded with our mobile phone microscope. In order to visualise the trajectories of all the sperm in the FOV, we construct an image where the sperm images for each frame in the movie are superimposed. The sperm images for each frame are then colour-coded by hue so that one can follow the sperm trajectories in time (Fig. 5b, Supplemental Movie 2). From this image, one can identify differences in motility patterns (e.g. Circular, forward progressive). This analysis gives a quick qualitative indication of the health of the semen sample, whereas a more quantitative picture can be obtained via tracking data. In brightfield mode, we found that up to 105 minutes of continuous video microscopy observation could be performed on a 2-year old iPhone 6 s battery.
Sperm imaging can also be achieved with much higher contrast in darkfield mode with solar illumination. Figure 5c is the first frame of an 11-second movie (Supplemental Movie 3) of a cattle semen sample (frozen/thawed) mounted between a microscope slide and coverslip. In this imaging modality, the tails of the sperm are clearly visible in addition to the sperm heads. One drawback of the high contrast in darkfield imaging is that other scattering structures in the semen sample (lipid aggregates from semen extenders, other seminal debris, etc…) also contribute the image, potentially confounding sperm tracking algorithms. Ideal tracking performance may require further sperm purification steps as is standard in computer-aided sperm analysis23.
Another application of our mobile phone microscope is on-site monitoring of microscopic aquatic life in ponds, streams, lakes or the ocean to complement more expensive underwater imagers24. We demonstrate zooplankton imaging by transferring a small amount of pond water (Carlton Gardens, Melbourne, Australia) directly into a glass capillary slide (G346-030-50, ProSciTech), and placing it in our microscope clip. We readily observe 1–5 zooplankton ranging in size from 0.05–0.3 mm within each capillary tube sample, a sampling of which are shown in Fig. 6a–d. The capillary slide is roughly the same width as the FOV (3 mm wide x 0.3 mm deep), so the entire sample can be scanned quickly by manually pulling the capillary slide through the FOV. A wide range of swimming and feeding behaviours can be observed (Supplementary Movies 4–7). Fast swimming zooplankton can easily be followed at 1x (Supplementary Movie 4) and 5x digital magnification (Supplementary Movie 5), by fine manual adjustment of the capillary slide position. When zooplankton are relatively stationary, a third party camera application20 can be used to focus through depth to observe 3D structure (Supplementary Movie 7).
We have designed a simple mobile phone microscope that takes advantage of the integrated illumination available with nearly all smartphone cameras. Our design requires no additional illumination optics, reducing cost and assembly complexity. The microscope is useable after one assembly step and requires only one extra component: a readily available mobile phone camera lens. With this design, we demonstrated both brightfield and darkfield microscopic imaging, including the visualization of cell nuclei in unlabelled cells and dynamic imaging of live cattle sperm and zooplankton. This device has the potential to be used as a general microscopy platform for a wide range of applications from biological fieldwork to microfluidic lab on a chip monitoring.
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This work has been supported by the ARC Centre of Excellence for Nanoscale BioPhotonics (CE140100003) and MicroNano Research Facility (MNRF) at RMIT University. B. C. G acknowledges the support of an ARC Future Fellowship (FT110100225). J. G. T. acknowledges the support of an NHMRC Research Fellowship (1077694).
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